WO2001022871A1 - Appareil optique capteur de glucose et procede - Google Patents

Appareil optique capteur de glucose et procede Download PDF

Info

Publication number
WO2001022871A1
WO2001022871A1 PCT/US2000/026659 US0026659W WO0122871A1 WO 2001022871 A1 WO2001022871 A1 WO 2001022871A1 US 0026659 W US0026659 W US 0026659W WO 0122871 A1 WO0122871 A1 WO 0122871A1
Authority
WO
WIPO (PCT)
Prior art keywords
light
concentration
field
polarization
solution
Prior art date
Application number
PCT/US2000/026659
Other languages
English (en)
Other versions
WO2001022871A9 (fr
Inventor
Martin D. Fox
Sunghoon Jang
Original Assignee
University Of Connecticut
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by University Of Connecticut filed Critical University Of Connecticut
Priority to AU77278/00A priority Critical patent/AU7727800A/en
Publication of WO2001022871A1 publication Critical patent/WO2001022871A1/fr
Publication of WO2001022871A9 publication Critical patent/WO2001022871A9/fr

Links

Classifications

    • 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
    • A61B5/14558—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 by polarisation
    • 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
    • G01N21/21—Polarisation-affecting properties

Definitions

  • the present invention relates to apparatus and methods of determining the glucose concentration of a glucose solution and more particularly, to an apparatus and method for non-invasive testing of the blood glucose of an individual based on measuring the optical rotation of glucose in the aqueous humor of the eye by optical methods.
  • Diabetes mellitus represents one of the major health problems today. Often, diabetes leads to such problems as renal failure and vision impairment. Estimated costs of diabetes related health care range between $20 to $40 billion annually. However, a recent multi-center NIH study has indicated that the health risks associated with diabetes are significantly reduced when the blood glucose levels are tightly controlled, indicating that it is prudent to measures the blood glucose as often as five or six times a day. Thus it is important that proper monitoring be done by diabetics at home or work.
  • a non-invasive method of testing an individual's blood glucose presently exists.
  • This non-invasive method reflects a beam of light through the aqueous humor glucose.
  • the method measures the polarization rotation of the beam to determine the concentration of the blood glucose.
  • US-A-5535743 attempts to overcome these problems by proposing the projection of a polarized beam of light onto the anterior face of the lens of the eye at an angle to the normal and the reflection of the light beam at an equal and opposite angle to the normal so that the light traverses twice through the anterior chamber and its aqueous humor.
  • the problem that will be caused by the cancellation of the optical rotation produced by passage through the aqueous humor of the incident beam when opposite rotation is produced in the reflected beam as it passes out through the aqueous humor is not recognized or addressed. We have appreciated that in practice, no measurable rotation will be observed.
  • US-A-5535743 discloses the use of a Faraday rotator in the light path to modulate the polarization of the light coupled with a lock in amplifier to improve the suppression of noise in the detection of the rotation.
  • EP-A-0805352 discloses a polarimetric method of determining the concentration of glucose in urine to which polarized light is passed through a Faraday rotator and then through a sample cell to a light sensor. It is further disclosed that the solenoid coil may be provided surrounding the sample cell so that the current needed in the coil to negate the optical rotation of the polarized light by the urine may be measured. In this arrangement, there is no recognition that the Verdet constant of glucose solution will be a function of the glucose concentration and no use is made of this phenomenon.
  • an apparatus for determining the concentration of optically active substances in a solution comprises a laser for producing a beam of light.
  • the beam of light passes through a coil having a predetermined number of turns.
  • the coil is disposed about at least a portion of the solution, preferably the aqueous humor of an eye.
  • An alternating current source is electrically connected to the coil to generate a magnetic field through the solution disposed therein.
  • An optical detector receives the beam of light after the beam passes through the portion of the solution and the coil. The optical detector provides an output signal indicative of the optical rotation of the solution, wherein the optical rotation is proportional to the concentration of the optically active substance.
  • a method for optically sensing concentration of optically active substance in a solution comprises generating a polarized beam of light and passing the beam through the solution.
  • a magnetic field is set up through the solution to provide a polarization of the vector of incident light, which is proportional to the concentration of the optically active substance in the solution.
  • the rotation of the polarization of the received polarized beam of light is determined.
  • the gyrotropic field may be any field which acting on the medium in which the measurement is being made (e.g. the aqueous humor of the eye) produces a rotation of the polarization vector of the light in a field dependent manner which further is a function of the concentration of the material of which the concentration is to be measured.
  • the field is preferably a magnetic field and the amount of rotation of the polarization vector of the light produced for a given field strength then depends on the Verdet constant of the medium which (despite the name Verdet constant) will be a function of the concentration of the material to be measured.
  • the gyrotropic field may alternatively in an appropriate case be an electric field.
  • the interface from which the light is reflected in the eye is preferably the anterior surface of the lens of the eye but could be the posterior surface of the lens, the iris, the retina, or the white of the eye.
  • the polarization of the light used in the method of the invention may be linear or circular but is preferably linear.
  • the magnetic field is preferably produced by a coil positioned in proximity to the eye
  • a permanent magnet may be used and variations in the magnetic field experienced within the aqueous humor may be produced in various ways including movement of the magnet itself or of a shield which shields the aqueous humor from the magnetic field to a varying degree according to its position.
  • the shield may be a second magnet or may be of material serving to block magnetic field lines such as mu metal.
  • the current driving the coil may have a DC component.
  • a combination of a coil and a permanent magnet may be used.
  • the light is preferably reflected back along substantially the same path by which it reached the interface in the eye, preferably the angle between the incident beam and the reflected beam is 0° but it may be up to 30°, more preferably up to 10°.
  • an apparatus for determining the concentration of an optically active substance in a solution comprising a light source for producing a beam of light arranged to direct said beam of light to pass through at least a portion of said solution; a source of magnetic field applied to at least said portion of the solution; an optical reflector a ⁇ anged with respect to said light source and said solution so as to reflect said beam of light to re-pass through at least said portion of said solution; an optical detector for receiving said beam of light after said re-passage through the solution in the presence of the magnetic field.
  • a method for measuring the concentration of a substance in a solution comprising the steps of measuring magneto-optical rotation produced in said solution, which rotation is indicative of the concentration dependent Verdet constant of the solution, and obtaining said concentration therefrom.
  • Figure 1 is a functional diagram of an optical glucose sensor embodying the present invention
  • Figure 2 is a diagrammatic view illustrative of reflective characteristics from a dielectric mirror of light passing through an optical rotatory medium
  • Figure 3 is a diagrammatic view illustrative of reflective characteristics from a dielectric mirror of light passing through a magnetic optical rotatory effect cell embodying the present invention
  • Figure 4 is an enlarged diagrammatic view of an eye with a detector beam reflecting off the aqueous humor passing through a magnetic field provided by the optical glucose sensor of Figure 1;
  • Figure 5 is a graphical illustration of the voltage output of the optical glucose sensor of Figure 1 for a single pass through the MORE cell;
  • Figure 6 is a graphical illustration of the voltage output of the optical glucose sensor of Figure 1 for a double pass through the MORE cell;
  • Figure 7 is a functional diagram of an alternative embodiment of an optical glucose sensor embodying the present invention.
  • Figure 8 shows the layout of optical components in a further preferred apparatus according to the invention.
  • Figure 9 shows the layout of optical components in a further preferred apparatus according to the invention.
  • a non-invasive optical glucose sensor 10 embodying the present invention is illustrated.
  • the glucose sensor 10 passes a beam of polarized light 12 through a glucose solution 14, which is reflected back through the solution.
  • the glucose solution has a Faraday effect, thus providing an optical rotatory medium (e.g., Faraday Rotator) that rotates the polarization of light passing therethrough.
  • the optical sensor 10 measures the polarization rotation of the reflected beam of light after passing through the glucose solution 14. It has been found that when a magnetic field (B) is set up in the glucose solution there is a rotation of the polarization of the vector of the incident light that is proportional to the path length, magnetic field strength and the concentration of the glucose in the solution.
  • B magnetic field
  • Figure 2 illustrates the reflection of a beam of light 12 passing through a cell of an optical rotatory medium 14 (i.e., a glucose solution) and reflecting back therethrough off a reflective surface 16, such as a dielectric surface.
  • an optical rotatory medium 14 i.e., a glucose solution
  • the geometry of the passage of the polarized beam 12 reflected through the cell 14 is shown graphically by the vector of the electric field (E) 18.
  • the direction of the E vector of the transmitted beam is shown at 20.
  • the effect of the beam of light 12 reflected from the dielectric minor 16 is similar to that of a conventional optical rotatory effect as is well know in the art.
  • the resulting rotation of the E vector 16, as shown at 22, is 180°, and thus cancels the reflection resulting in zero net optical rotation.
  • Figure 3 illustrates the reflection of a beam of light 12 through a cell 14 of a similar optical medium, as shown in Figure 2, wherein a magnetic field (B) is set up in the optical rotatory medium by conducting an alternating cu ⁇ ent through the coil 24 disposed about the medium.
  • the cell of Figure 3 uses the magnetic Optical Rotator Effect ("MORE") to achieve double the rotation (2 ⁇ ) in the same geometry.
  • MORE magnetic Optical Rotator Effect
  • This double rotation is achieved because the direction of rotation is dependent on the vector cross product B x E, and the direction of B remains in the same direction as indicated by arrows 26.
  • the direction of the E vector 18 of the transmitted beam is shown at 28.
  • the reflection of the light beam 12 from the dielectric minor 16 and magnetic optical rotatory effect cell 14 with glucose solution results in 180 degree rotation of E vector 18 (due to the mirror reflection) with an additional 2 ⁇ phase shift, as shown at 30.
  • This method eliminates the cancellation of the conventional optical rotation effect that occurs upon reflection from a dielectric [E field inverting] minor.
  • This method of optically sensing the concentration of glucose in a solution 14 disposed in the aqueous humor 31 in accordance with the present invention may be used to provide a non-invasive procedure to determine the glucose level of an individual by reflecting the beam of light 12 off the lens 32 in the human eye 34 as illustrated in Figure 4.
  • the lens/aqueous interface can be characterized as a dielectric minor 16.
  • the magnetic optical rotation effect should double the detected rotation. The double rotation is due to the light beam 12 passing twice through the glucose in the aqueous humor 14 with magnetic field (B) after reflection of the light beam 12 from the aqueous/lens interface.
  • optical glucose sensor 10 is similar in a number aspects as that disclosed in the articles "Multiple Wavelength Non- Invasive Ocular Polarimetry for Glucose Measurement for Managing of Diabetes", published in SBIR Program Final Report, 1995; and "Optical Glucose Sensor Using a Single Faraday Rotator, published in Proceedings of the 23 rd Annual Northeast Bioengineering Conference, May 21-22, 1997; each of which are hereinafter incorporated by reference.
  • a coherent light source 36 cunently a helium neon (HeNe) laser, emits a collimated beam 12.
  • the light source may be a white light source.
  • the light from such a white light source should preferably be made monochromatic by the use of suitable filters or a diffraction grating.
  • suitable non-temporally coherent light sources include led's, incandescent light bulbs, and gas discharge lamps, for instance a sodium lamp, a deuterium lamp, an iodine quartz lamp or a xenon flash lamp.
  • the light frequency employed in the invention may be selected to be especially eye-safe, being a frequency which is well absorbed in the vitreous humor and which will therefore be attenuated before it reaches the retina. Measurements may be carried out at two or more light frequencies so as to enable the elimination of the effects of confounder substances present in the aqueous humor by virtue of the difference in the light frequency dependency of their f(C m ). Multiple light frequencies may be used.
  • the beam 12 is then passed through a first polarizer (PI) 38, which linearly polarizes the light of the beam to produce a field (E).
  • the laser 36 provides approximately 2 mW effective output after the first polarizer 38 of 633 nm.
  • the light beam 12 then passes through a Faraday rotator (FR) 40 which rotates the polarization of the beam approximately 5°. This degree of rotation is dependent on the level of the voltage, which may be increased by increasing the voltage provided to the Faraday rotator.
  • FR Faraday rotator
  • a function generator 42 provides an approximately 1.2 kHz drive signal to the Faraday rotator 40.
  • the light beam 12 then passes through the cell 14 (MORE cell) of glucose solution (e.g., the aqueous solution of the aqueous humor 31) and reflects back through the cell, as shown in Figure 3.
  • a coil 24 of a predetermined number of turns is electrically connected to an alternating cunent (ac) source 44.
  • the number of turns of the coil is based on the desired magnitude of the magnetic field (B). In one embodiment, the number of turns is greater than 100.
  • the frequency of the ac source for example, may be approximately 10 Hz, however, one skilled in the art will appreciate that signal to noise ratio improves as the frequency of the ac source increases.
  • the coil 24 winds about the cell 14, such that the longitudinal axis of the coil is generally perpendicular to the reflective interface 16.
  • the ac source 44 and the coil 24 generate a magnetic field (B) throughout the glucose solution, which can be precisely controlled.
  • the inner diameter of the coil 24 is substantially equal to the diameter of the human eye (i.e., the cell).
  • the coil 24 is place within the user's eye socket so that a portion of the eye 34 is disposed within the coil.
  • the reflected beam 12 then passes through the coil and the glucose solution of the aqueous humor 31 within the eye 34 and reflects off the lens 32 and back through the solution and coil.
  • the light beam 12 then passes through a second polarizer (P2) 46, which is disposed at 90 degrees to the first polarizer 38.
  • the resulting rotation of the polarized beam passing through the second polarizer 46 is determined by a photomultipher tube (PMT) 48 that generates an electrical output signal at lead 50 representative of the rotational position of the beam 12.
  • the output signal is fed back to the Faraday rotator 40 through a lock-in or phase lock amplifier 52, an electronic circuit 54 and a two (2) Henry inductor 56 to close the loop.
  • the output signal is also provided to an oscilloscope 60 via lead 58 for displaying the output signal.
  • the output signal from the photomultipher tube 48 and the lock-in amplifier 52 may be provided to a processor that generates a phase signal indicative of the phase rotation of the glucose in the aqueous humor 31.
  • the phase signal is provided to a readout, which displays a result indicative of the concentration of the glucose in the aqueous humor.
  • the lock-in amplifier 52 provides an output signal, which is a dc voltage proportional to the amplitude of the 1.2 kHz present in the output signal from the photomultipher 48. This dc output voltage is fed back to an integrator of the electronic circuit 54 and the Faraday rotator 40 through the inductor 56 to close the loop.
  • the lock-in amplifier 52 therefore provides phase and frequency locked detection of the 1.2 kHz component, which is proportional to the net rotation between the two polarizers 38 and 46 disposed at 90° to each other.
  • the bandpass of the feedback loop also limits the lock-in frequency. As described hereinbefore, increasing the lock in frequency increase the signal to noise ratio of the system.
  • the MORE cell 14 varies or modulates this net rotation at the frequency of the magnetic field (B), which may be set at approximately 10 Hz (frequency of the ac source 44).
  • the resultant signal is picked up as a 10 Hz p-p ac signal on the oscilloscope 60.
  • the function generator also provides the 1.2 kHz signal to the lock-in amplifier. This AC modulation of the desired signal, which can be detected using the lock-in amplifier 52 for phase coherent detection, results in improved signal to noise ratio.
  • This lock-in technique can actually pull a signal out of over 100 db of additive random noise.
  • the beam of light 12 passes through the magnetic optical rotatory cell 14 after reflection from the dielectric minor 16, the magnitude of rotation due to the MORE cell is proportional to the concentration of the glucose, the path length of the cell, and the magnitude of the magnetic field (B) in the cell.
  • a single magnetic optical rotatory effect (MORE) cell may be used to sense the optical rotation of a glucose solution.
  • MORE magnetic optical rotatory effect
  • a single MORE cell is similar to that described hereinabove except the light 12 is not reflected back through the cell 14 (glucose solution), but reflected directly to the second polarizer 46.
  • Figures 5 and 6 illustrate graphically the peak to peak voltage of the output signal of the optical sensor 10 versus the glucose concentration of the solution for a single MORE cell and double MORE cell, respectively.
  • Vp-p peak-peak voltage output is from the lock-in amplifier 52; and G is the concentration of glucose solution in mg/dl.
  • the double MORE cell provides twice the optical rotation of the single pass of the single MORE cell, and thus showing that the double MORE had 99.7% greater slope (close to the predicted 100% greater slope) indicating twice the sensitivity of single MORE cell.
  • an alternative embodiment of an optical glucose sensor 70 is shown. Like numbered components of the sensor 10 illustrated in Figure 1 and described hereinbefore are similar to sensor 70 shown in Figure 7.
  • the glucose sensor 70 of Figure 7 further includes an additional lock in amplifier 72 for a second feedback loop to improve the signal to noise ratio of the sensor.
  • the output signal of the first lock in amplifier 52 is provided to the input of the second lock in amplifier 70.
  • the ac source 44 is provided to the input of the second lock in amplifier 70.
  • the output of the second lock in amplifier is then provided to the oscilloscope 60 (or processor).
  • an alternative detection strategy is to vary the maximum intensity of the field by adjustment of the ac voltage/cunent applied to the coil in Figure 7 to produce a predetermined level of optical rotation and to use the cunent applied to the coil or the cunent flowing in it as a measure of the concentration.
  • the lock in amplifier may instead be coupled to the ac source 44, and the Faraday rotator 40 may be omitted.
  • Figure 8 shows apparatus for measuring the concentration of a substance such as glucose within the aqueous humor of the eye, in which the optical components described previously are ananged in a prefened optical geometry.
  • the light source 36 directed through the polarizer 38 and through the Faraday rotator 40, as in Figure 1.
  • a half silvered minor Ml is interposed between the Faraday rotator 40 and the eye.
  • Coil 24 is ananged sunounding the front of the eye.
  • the light beam 12 enters the eye normal to the anterior surface of the lens via the aqueous humor and is reflected back along the same path to the minor Ml from which it is reflected to a second minor M2 and from there to the second polarizer 46 to the optical detector 48.
  • the electronic components are connected to the optical components as shown in Figure 1 or Figure 7.
  • Figure 9 shows a further prefened optical geometry.
  • Light from a light source 36 is directed through a linear polarizer 38 and a Faraday rotator 40 and then to a beam spreader and spatial filter 90.
  • the broadened beam then passes through a glass plate 92, the right hand half of which is silvered on the face nearer the eye. Thus only the left hand part of the broadened beam is passed on and the right hand half is blocked.
  • There is then a lens system 94 focusing the beam on the anterior surface of the eye lens.
  • the solenoid coil 24 sunounds the front of the eye.
  • Light reflected from the eye lens is directed back toward the light source and is spread by the lens system 94 before impinging on the plate 92. That part of the reflected light falling on the silvered part of the plate is reflected across to a minor 96 and via a lens 98 and an aperture plate 100 to a polarizer 46 and to the photodetector 48.
  • the use of the part silvered plate 92 and the focusing of the reflected light through the aperture plate 100 serves to exclude reflections from other interfaces in the eye such as the surfaces of the cornea from reaching the photodetector.
  • Advantages of this anangement over that in which the light is incident on the lens at an angle off the normal and is reflected therefrom at an equal angel to the opposite side of the normal plane are that complexities in the effect of reflection on the polarization of the light are reduced by the absence of light components parallel to the reflecting surface and the apparatus is made physically easier to align and to focus on the desired reflecting surface. Adjustment for differing optical characteristics of different eyes may be made by movement of one component, namely the lens system 94.
  • the magneto-optical rotation which is measured is that produced by the Faraday effect as the light passes through a solution of a substance whose concentration is to be measured and the amount of rotation is determined by the variation with concentration of said substance of the Verdet constant of the solution for the light wavelength used.
  • the present invention described hereinbefore for optically sensing glucose using the fact that magnetically induced optical rotation in glucose solutions is linearly proportional to glucose concentration at physiologic levels has many advantages over the prior art.
  • This non-invasive method of testing blood glucose is fast and simple, and is more economical than existing methods. The cost to patients of such a method would be significantly less over time than existing methods because only a monitor 10 would be required, and the high monthly expense of testing strips would be avoided. In addition, patient acceptance would be very high because of the non-invasive nature and the simple use of the procedure.
  • the present invention produces improved spatial resolution since the effect only occurs in regions of space where the magnetic field distribution can be precisely controlled. Improved signal to noise ratio can also be achieved due to an AC modulation of the desired signal which can be detected using a lock in amplifier for phase coherent detection. This lock-in technique can actually pull a signal out of over 100 db of additive random noise.
  • the magnetic field (B) provided about the cell 14 of glucose solution eliminates the cancellation of the conventional optical rotation effect that occurs upon reflection from a dielectric [E field inverting] minor 16. This makes possible glucose measurements after reflection from the aqueous/lens interface.
  • the apparatus and method are adaptable to other applications where an optically active substance is to be measured.
  • some biogenetic processes have optically active materials either as reactants or products, and the apparatus and method may be used as a non-invasive tool to follow the progress of the reaction without the potential for contamination presented by sampling devices.

Landscapes

  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Pathology (AREA)
  • General Health & Medical Sciences (AREA)
  • Surgery (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Optics & Photonics (AREA)
  • Animal Behavior & Ethology (AREA)
  • Biophysics (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Chemical & Material Sciences (AREA)
  • Analytical Chemistry (AREA)
  • Biochemistry (AREA)
  • General Physics & Mathematics (AREA)
  • Immunology (AREA)
  • Investigating Or Analysing Materials By Optical Means (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

La présente invention concerne un appareil non invasif et un procédé permettant de capter optiquement la concentration de glucose contenue dans une solution. Ce capteur (10) optique de glucose est fondé sur le fait que les solutions de glucose ont des effets magnétiques de rotation optique (MORE) si bien que lorsqu'on crée un champ magnétique dans une solution de glucose, on assiste à une rotation du vecteur de polarisation de la lumière incidente qui est proportionnelle à la longueur du trajet, à la force du champ magnétique et à la concentration de glucose contenue dans cette solution. Ce capteur (10) optique de glucose comprend un laser (36) qui fait passer un faisceau de lumière polarisée (12) à travers la solution de glucose (par exemple une humeur aqueuse ou un oeil) tandis qu'une bobine (24) crée un champ magnétique (B) dans la solution. Un tube photomultiplicateur (48) fournit un signal de sortie indicatif de la rotation du vecteur de polarisation de la lumière incidente. Le faisceau de lumière (12) est également modulé par un rotateur de Faraday (46) commandé par un amplificateur (52) enclenché qui ferme une boucle de rétroaction. La sortie de l'amplificateur (52) enclenché génère un signal indicatif de la concentration de glucose contenue dans la solution, qui peut être affiché sur un oscilloscope (60) ou fourni à un processeur, lequel affiche une sortie indicative de la concentration de glucose.
PCT/US2000/026659 1999-09-28 2000-09-28 Appareil optique capteur de glucose et procede WO2001022871A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU77278/00A AU7727800A (en) 1999-09-28 2000-09-28 Optical glucose sensor apparatus and method

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US40721099A 1999-09-28 1999-09-28
US09/407,210 1999-09-28

Publications (2)

Publication Number Publication Date
WO2001022871A1 true WO2001022871A1 (fr) 2001-04-05
WO2001022871A9 WO2001022871A9 (fr) 2002-10-03

Family

ID=23611105

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2000/026659 WO2001022871A1 (fr) 1999-09-28 2000-09-28 Appareil optique capteur de glucose et procede

Country Status (2)

Country Link
AU (1) AU7727800A (fr)
WO (1) WO2001022871A1 (fr)

Cited By (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1912058A1 (fr) 2006-10-14 2008-04-16 Roche Diagnostics GmbH Dispositif et procédé pour la détection et l'évaluation des signaux optiques
DE102008003444A1 (de) * 2008-01-07 2009-07-09 Hochschule Offenburg Vorrichtung zum Ermitteln eines Konzentrationswertes, Verwendung, Verfahren und Computerprogrammprodukt
CN102755167A (zh) * 2011-04-29 2012-10-31 财团法人工业技术研究院 非侵入式血糖监测装置与方法以及生化分子的分析方法
US9101308B2 (en) 2012-10-16 2015-08-11 K Sciences Gp, Llc Simple sugar concentration sensor and method
TWI495864B (zh) * 2012-04-27 2015-08-11 Taiwan Biophotonic Corp 非侵入式血糖監測裝置與方法以及生化分子的分析方法
US9442065B2 (en) 2014-09-29 2016-09-13 Zyomed Corp. Systems and methods for synthesis of zyotons for use in collision computing for noninvasive blood glucose and other measurements
CN106061385A (zh) * 2014-03-12 2016-10-26 索尼公司 测量装置和测量方法
US9554738B1 (en) 2016-03-30 2017-01-31 Zyomed Corp. Spectroscopic tomography systems and methods for noninvasive detection and measurement of analytes using collision computing
US9662004B2 (en) 2011-04-29 2017-05-30 Taiwan Biophotonic Corporation Apparatus for non-invasive glucose monitoring
US9724022B2 (en) 2011-04-29 2017-08-08 Taiwan Biophotonic Corporation Apparatus for non-invasive glucose monitoring
US10067054B2 (en) 2012-10-16 2018-09-04 K Sciences Gp, Llc Simple sugar concentration sensor and method
US11426100B1 (en) 2015-12-08 2022-08-30 Socrates Health Solutions, Inc. Blood glucose trend meter

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3958560A (en) 1974-11-25 1976-05-25 Wayne Front March Non-invasive automatic glucose sensor system
US5535743A (en) 1992-12-19 1996-07-16 Boehringer Mannheim Gmbh Device for the in vivo determination of an optical property of the aqueous humour of the eye
WO1997034521A1 (fr) * 1996-03-19 1997-09-25 Abbott Laboratories Mesure non invasive de composes a activite optique
EP0805352A1 (fr) 1995-11-16 1997-11-05 Matsushita Electric Industrial Co., Ltd. Procede et appareil d'analyse d'urine, procede de mesure de la rotation optique et polarimetre
EP0902270A1 (fr) * 1997-09-09 1999-03-17 Matsushita Electric Industrial Co., Ltd. Cellule d'échantillon pour polarimétrie, polarimètre, et procédé polarimétrique

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3958560A (en) 1974-11-25 1976-05-25 Wayne Front March Non-invasive automatic glucose sensor system
US5535743A (en) 1992-12-19 1996-07-16 Boehringer Mannheim Gmbh Device for the in vivo determination of an optical property of the aqueous humour of the eye
EP0805352A1 (fr) 1995-11-16 1997-11-05 Matsushita Electric Industrial Co., Ltd. Procede et appareil d'analyse d'urine, procede de mesure de la rotation optique et polarimetre
WO1997034521A1 (fr) * 1996-03-19 1997-09-25 Abbott Laboratories Mesure non invasive de composes a activite optique
EP0902270A1 (fr) * 1997-09-09 1999-03-17 Matsushita Electric Industrial Co., Ltd. Cellule d'échantillon pour polarimétrie, polarimètre, et procédé polarimétrique

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
BROWNE A F ET AL: "MICRODEGREE POLARIMETRIC MEASUREMENT OF GLUCOSE CONCENTRATIONS FOR BIOTECHNOLOGY APLLICATIONS", PROCEEDINGS OF THE IEEE NORTHEAST BIOENGINEERING CONFERENCE,US,NEW YORK, IEEE, vol. CONF. 23, 21 May 1997 (1997-05-21), pages 9 - 10, XP000738103, ISBN: 0-7803-3849-9 *
JANG SUNGHOON AND FOX MARTIN D.: "Double Lock-in Concept for MORE Clucose Detection", PROCEEDINGS OF THE IEEE 25TH ANNUAL NORTHEAST BIOENGINEERING CONFERENCE (CAT. NO. 99CH36355) WEST HARTFORD, CT, USA, 8 April 1999 (1999-04-08) - 9 April 1999 (1999-04-09), pages 122 - 124, XP002155401 *

Cited By (30)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1912058A1 (fr) 2006-10-14 2008-04-16 Roche Diagnostics GmbH Dispositif et procédé pour la détection et l'évaluation des signaux optiques
US7630084B2 (en) 2006-10-14 2009-12-08 Roche Diagnostics Operations, Inc. System and method for acquiring and evaluating optical signals
DE102008003444A1 (de) * 2008-01-07 2009-07-09 Hochschule Offenburg Vorrichtung zum Ermitteln eines Konzentrationswertes, Verwendung, Verfahren und Computerprogrammprodukt
US9724022B2 (en) 2011-04-29 2017-08-08 Taiwan Biophotonic Corporation Apparatus for non-invasive glucose monitoring
US9833175B2 (en) 2011-04-29 2017-12-05 Taiwan Biophotonic Corporation Apparatus for non-invasive blood glucose monitoring
US9662004B2 (en) 2011-04-29 2017-05-30 Taiwan Biophotonic Corporation Apparatus for non-invasive glucose monitoring
CN105266824A (zh) * 2011-04-29 2016-01-27 台医光电科技股份有限公司 非侵入式血糖监测装置与方法以及生化分子的分析方法
CN102755167A (zh) * 2011-04-29 2012-10-31 财团法人工业技术研究院 非侵入式血糖监测装置与方法以及生化分子的分析方法
EP2517624A3 (fr) * 2011-04-29 2013-03-20 Industrial Technology Research Institute Appareil et procédé de surveillance non invasive de la glycémie et procédé pour analyser une molécule biologique
US9743864B2 (en) 2011-04-29 2017-08-29 Taiwan Biophotonic Corporation Method for non-invasive blood glucose monitoring and method for analysing biological molecule
US10631763B2 (en) 2011-04-29 2020-04-28 Taiwan Biophotonic Corporation Method for glucose monitoring
TWI495864B (zh) * 2012-04-27 2015-08-11 Taiwan Biophotonic Corp 非侵入式血糖監測裝置與方法以及生化分子的分析方法
US11092543B2 (en) 2012-10-16 2021-08-17 K Sciences Gp, Llc Simple sugar concentration sensor and method
US10067054B2 (en) 2012-10-16 2018-09-04 K Sciences Gp, Llc Simple sugar concentration sensor and method
US10481085B2 (en) 2012-10-16 2019-11-19 K Sciences Gp, Llc Simple sugar concentration sensor and method
US9636052B2 (en) 2012-10-16 2017-05-02 K Sciences Gp, Llc Simple sugar concentration sensor and method
US11781982B2 (en) 2012-10-16 2023-10-10 K Sciences Gp, Llc Simple sugar concentration sensor and method
US9320463B2 (en) 2012-10-16 2016-04-26 K Sciences Gp, Llc Simple sugar concentration sensor and method
US9101308B2 (en) 2012-10-16 2015-08-11 K Sciences Gp, Llc Simple sugar concentration sensor and method
CN106061385A (zh) * 2014-03-12 2016-10-26 索尼公司 测量装置和测量方法
US9610018B2 (en) 2014-09-29 2017-04-04 Zyomed Corp. Systems and methods for measurement of heart rate and other heart-related characteristics from photoplethysmographic (PPG) signals using collision computing
US9459202B2 (en) 2014-09-29 2016-10-04 Zyomed Corp. Systems and methods for collision computing for detection and noninvasive measurement of blood glucose and other substances and events
US9459203B2 (en) 2014-09-29 2016-10-04 Zyomed, Corp. Systems and methods for generating and using projector curve sets for universal calibration for noninvasive blood glucose and other measurements
US9459201B2 (en) 2014-09-29 2016-10-04 Zyomed Corp. Systems and methods for noninvasive blood glucose and other analyte detection and measurement using collision computing
US9453794B2 (en) 2014-09-29 2016-09-27 Zyomed Corp. Systems and methods for blood glucose and other analyte detection and measurement using collision computing
US9448165B2 (en) 2014-09-29 2016-09-20 Zyomed Corp. Systems and methods for control of illumination or radiation collection for blood glucose and other analyte detection and measurement using collision computing
US9448164B2 (en) 2014-09-29 2016-09-20 Zyomed Corp. Systems and methods for noninvasive blood glucose and other analyte detection and measurement using collision computing
US9442065B2 (en) 2014-09-29 2016-09-13 Zyomed Corp. Systems and methods for synthesis of zyotons for use in collision computing for noninvasive blood glucose and other measurements
US11426100B1 (en) 2015-12-08 2022-08-30 Socrates Health Solutions, Inc. Blood glucose trend meter
US9554738B1 (en) 2016-03-30 2017-01-31 Zyomed Corp. Spectroscopic tomography systems and methods for noninvasive detection and measurement of analytes using collision computing

Also Published As

Publication number Publication date
WO2001022871A9 (fr) 2002-10-03
AU7727800A (en) 2001-04-30

Similar Documents

Publication Publication Date Title
WO2000060350A2 (fr) Appareil et procede de detection optique de glucose
US6999808B2 (en) Method and device for glucose concentration measurement with special attention to blood glucose determinations
US6885882B2 (en) Method and apparatus for non-invasive glucose sensing through the eye
JP3184521B2 (ja) 濃度を決定するための測定装置及び測定システム
US5398681A (en) Pocket-type instrument for non-invasive measurement of blood glucose concentration
US5137023A (en) Method and apparatus for monitoring blood analytes noninvasively by pulsatile photoplethysmography
US6152875A (en) Glucose concentration measuring method and apparatus
JP2736002B2 (ja) 眼の房水の光学的性質のインビボ測定用デバイス
US5183042A (en) Electromagnetic method and apparatus to measure constituents of human or animal tissue
US5372135A (en) Blood constituent determination based on differential spectral analysis
US6442410B1 (en) Non-invasive blood glucose measurement system and method using optical refractometry
US5178142A (en) Electromagnetic method and apparatus to measure constituents of human or animal tissue
US5560356A (en) Diagnostic system and method using an implanted reflective device
US6370407B1 (en) System for improving the sensitivity and stability of optical polarimetric measurements
US7248905B2 (en) Method of and apparatus for measuring concentration
US20160192867A1 (en) Wearable, noninvasive glucose sensing methods and systems
JP3224540B2 (ja) ヒト又は動物の組織の成分を測定するための装置
US20110299066A1 (en) Component concentration meter, component concentration measurement method, shipping inspection system, and health management system
JPH09512722A (ja) 生物学的試料に含まれるグルコースの分析のための方法および装置
EP2528490B1 (fr) Surveillance oculaire non invasive
EP2909624B1 (fr) Détecteur de concentration de sucre simple et procédé associé
EP1740087A2 (fr) Polarimetre de detection a compensation de la birefringence non-invasif
EP0626819A1 (fr) Mesure non invasive de la glycemie
WO2001022871A1 (fr) Appareil optique capteur de glucose et procede
US20100234704A1 (en) Non-Invasive Polarimetric Apparatus and Method for Analyte Sensing in Birefringent Media

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AE AL AM AT AU AZ BA BB BG BR BY CA CH CN CR CU CZ DE DK DM EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MA MD MG MK MN MW MX NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT TZ UA UG UZ VN YU ZA ZW

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): GH GM KE LS MW MZ SD SL SZ TZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG

121 Ep: the epo has been informed by wipo that ep was designated in this application
REG Reference to national code

Ref country code: DE

Ref legal event code: 8642

122 Ep: pct application non-entry in european phase
AK Designated states

Kind code of ref document: C2

Designated state(s): AE AL AM AT AU AZ BA BB BG BR BY CA CH CN CR CU CZ DE DK DM EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MA MD MG MK MN MW MX NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT TZ UA UG UZ VN YU ZA ZW

AL Designated countries for regional patents

Kind code of ref document: C2

Designated state(s): GH GM KE LS MW MZ SD SL SZ TZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG

COP Corrected version of pamphlet

Free format text: PAGES 1/6-6/6, DRAWINGS, REPLACED BY NEW PAGES 1/5-5/5; DUE TO LATE TRANSMITTAL BY THE RECEIVING OFFICE

NENP Non-entry into the national phase

Ref country code: JP