Self-emission noninvasive infrared spectrophotometer with body temperature compensation

• US 5,615,672 A
• Filed: 12/09/1994
• Issued: 04/01/1997
• Est. Priority Date: 01/28/1993
• Status: Expired due to Fees

• Current Assignee: Optiscan Pty Ltd.
• Original Assignee: Optiscan Pty Ltd.
• Inventors: Braig, James R., Sterling, Bernhard B., Goldberger, Daniel S.
• Primary Examiner(s): Sykes, Angela D.
• Assistant Examiner(s): WINAKUR, ERIC FRANK
• Application Number:
  US08/353,099
• Time in Patent Office: 844 Days
• Field of Search: 128/633, 128/664
• US Class Current: 600/474
• CPC Class Codes: A61B 5/14532 for measuring glucose, e.g. by tissue impedance measurement
• CPC Class Codes: A61B 5/14546 for measuring analytes not otherwise provided for, e.g. ions, cytochromes
• CPC Class Codes: A61B 5/1455 using optical sensors, e.g. spectral photometrical oximeters
• CPC Class Codes: G01N 21/35 using infrared light G01N21/39 takes precedence
• CPC Class Codes: G01N 21/3581 using far infrared light; using Terahertz radiation

Abstract

A method and apparatus for monitoring glucose, ethyl alcohol and other blood constituents in a noninvasive manner. The measurements are made by monitoring infrared absorption of the desired blood constituent in the long infrared wavelength range where the blood constituent has a strong and distinguishable absorption spectrum. The long wavelength infrared energy emitted by the person as heat is monitored and the infrared absorption of particular constituents in the blood (such as glucose or blood alcohol) is measured at characteristic infrared absorption wavelengths for those constituents. The measurements are preferably synchronized with systole and diastole of the cardiac cycle so that the signal contribution caused by veins and tissues (which do not pulse) may be cancelled when a ratio of the detected signals is taken. On the other hand, if no synchronization is provided, the spectrophotometer may measure the arterial, venous and tissue constituent concentrations simultaneously, which may be desired in some circumstances. The internal "blackbody" energy level of an infrared emissions source such as a vascularized appendage prior to glucose absorption is measured and used to compensate temperature dependent effects in the concentration calculation. The internal energy level is then ratioed to the actual measured energy and used to compute the percentage of energy absorbed by the glucose. Discontinuities in the ratio are eliminated by converting the absorption measurements from voltages to watts.

Claims

1. A noninvasive infrared spectrophotometer, comprising:

means for detecting infrared emissions generated and emitted by a vascularized appendage of a person;

means for determining infrared absorption of at least one predetermined constituent of the person'"'"'s blood from said infrared emissions detected by said detecting means;

means for measuring an internal temperature of said person at a point of said vascularized appendage where said infrared emissions are detected by said detecting means; and

processing means for determining the infrared emissions corresponding to said internal temperature measured by said temperature measuring means and for calculating a concentration of said at least one predetermined constituent as a function of the infrared emissions detected by said detecting means and the determined infrared emissions corresponding to said internal temperature measured by said temperature measuring means.

2. A spectrophotometer as in claim 1, further comprising synchronizing means for synchronizing the detection of said infrared emissions by said detecting means with systolic and diastolic phases of a cardiac cycle of the person.

3. A spectrophotometer as in claim 1, wherein said temperature measuring means comprises an RTD which is adapted to be wrapped around the person'"'"'s arm.

4. A spectrophotometer as in claim 3, wherein said temperature measuring means further comprises an insulating material adapted to be wrapped around the person'"'"'s arm so as to cover said RTD.

5. A spectrophotometer as in claim 1, wherein said processing means calculates the concentration C of said at least one predetermined constituent in accordance with the equation:

space="preserve" listing-type="equation">I/I.sub.o =e.sup.--CLX,

where L is a pathlength from a point within said vascularized appendage where said infrared emissions originate to said detecting means, X is an experimentally determined extinction coefficient, I is the infrared emissions detected by said detecting means, and I_o is the incident energy within said vascularized appendage, defined from Planck'"'"'s equation as;

##EQU5## where T_R is a transmission coefficient of a filter which passes said at least one predetermined constituent, e is emissivity of skin, C₁ =3.74×

10⁴, C₂ =1.438×

10⁴, T is the internal temperature of said person at said point where said infrared emissions originate, and λ

is a wavelength of said filter.

6. A noninvasive infrared spectrophotometer for determining a concentration of at least one predetermined constituent in a person'"'"'s blood, comprising:

means for detecting infrared energy generated and emitted by the person in a wavelength range including n different wavelengths of at least 2.0 μ

m, said infrared energy containing energy at each of said n wavelengths which is differently absorbed by said at least one predetermined constituent whereby each predetermined constituent readily absorbs infrared energy at least one of said n wavelengths and minimally absorbs infrared energy at another of said n wavelengths, said detecting means outputting at least one detection signal representative of infrared energy at said n wavelengths which has been emitted by said person and selectively absorbed by said at least one predetermined constituent;

means for measuring an internal temperature of said person at a point of said person where said infrared energy is detected by said detecting means; and

processing means for determining the infrared emissions corresponding to said internal temperature measured by said temperature measuring means and for calculating the concentration of said at least one predetermined constituent as a function of the infrared energy detected by said detecting means and the determined infrared emissions corresponding to said internal temperature measured by said temperature measuring means.

7. A spectrophotometer as in claim 6, wherein said infrared energy is detected by said detecting means during a diastolic time interval of a diastolic phase of the cardiac cycle of the person and during a systolic time interval of a systolic phase of the cardiac cycle of the person, said systolic and diastolic time intervals each having a duration of approximately 0.1-10 msec during the systolic and diastolic phases, respectively, of said cardiac cycle of the person.

8. A spectrophotometer as in claim 6, wherein said at least one predetermined constituent includes glucose, said one wavelength is approximately 9.1 μ

m and said another wavelength is approximately 10.5 μ

m.

9. A spectrophotometer as in claim 8, further comprising an analytical filter wheel including first and second bandpass filters disposed between an arterial blood vessel of the person and said detecting means, said first bandpass filter passing infrared light in a narrow passband centered at approximately 9.1 μ

m, and said second bandpass filter passing infrared light in a narrow passband centered at approximately 10.5 μ

m.

10. A spectrophotometer as in claim 8, further comprising a first bandpass filter disposed between an arterial blood vessel of the person and said detecting means, said first bandpass filter passing infrared light in a narrow passband centered at approximately 9.1 μ

m, and a second bandpass filter disposed between the arterial blood vessel of the person and said detecting means, said second bandpass filter passing infrared light in a narrow passband centered at approximately 10.5 μ

m.

11. A spectrophotometer as in claim 6, wherein said at least one predetermined constituent includes ethyl alcohol, said one wavelength is approximately 3.4 μ

m and said another wavelength is approximately 4.8 μ

m.

12. A spectrophotometer as in claim 11, further comprising an analytical filter wheel including first and second bandpass filters disposed between an arterial blood vessel of the person and said detecting means, said first bandpass filter passing infrared light in a narrow passband centered at approximately 3.4 μ

m, and said second bandpass filter passing infrared light in a narrow passband centered at approximately 4.8 μ

m.

13. A spectrophotometer as in claim 11, further comprising a first bandpass filter disposed between an arterial blood vessel of the person and said detecting means, said first bandpass filter passing infrared light in a narrow passband centered at approximately 3.4 μ

m, and a second bandpass filter disposed between the arterial blood vessel of the person and said detecting means, said second bandpass filter passing infrared light in a narrow passband centered at approximately 4.8 μ

m.

14. A spectrophotometer as in claim 6, further comprising synchronizing means for synchronizing the detection of said infrared energy by said detecting means with systolic and diastolic phases of a cardiac cycle of the person.

15. A spectrophotometer as in claim 14, wherein said synchronizing means includes a cardiac monitor and plethysmograph sensing means for detecting said systolic and diastolic phases of the cardiac cycle of the person from well perfused tissue of the person.

16. A spectrophotometer as in claim 15, wherein said plethysmograph sensing means comprises a pulsed light emitting diode which directs light through said well perfused tissue of the person and a photodetector which detects the light which has passed through said well perfused tissue of the person, and said cardiac monitor comprises processing means for processing a detection output of said photodetector to determine a phase of said cardiac cycle.

17. A spectrophotometer as in claim 6, wherein said processing means calculates the concentration C of said at least one predetermined constituent in accordance with the equation:

space="preserve" listing-type="equation">I/I.sub.o =e.sup.--CLX,

where L is a pathlength from a point within said person where said infrared energy originates to said point where said infrared energy is detected by said detecting means, X is an experimentally determined extinction coefficient, I is the infrared energy detected by said detecting means, and I_o is the incident energy within said person where said internal temperature is measured, defined from Planck'"'"'s equation as;

##EQU6## where T_R is a transmission coefficient of a filter which passes said at least one predetermined constituent, ε

is emissivity of skin, C₁ =3.74×

10⁴, C₂ =1.438×

10⁴, T is the internal temperature of said person at said point of said person where said infrared energy originates, and λ

is a wavelength of said filter.

18. A spectrophotometer as in claim 6, further comprising a chopper wheel which modulates said infrared energy emitted by the person to a frequency beyond baseband prior to detection by said detecting means, a preamplifier which amplifies said at least one detection signal, a bandpass filter centered at said frequency beyond baseband, and a synchronous demodulator which demodulate said demodulation signal from said frequency beyond baseband.

19. A spectrophotometer as in claim 18, wherein said processing means forms a ratio R=(Sys L1-Dias L1)/(Sys L2-Dias L2), where Sys L1 is a detected systolic phase signal at said one wavelength, Dias L1 is a detected diastolic phase signal at said one wavelength, Sys L2 is a detected systolic phase signal at said another wavelength, and Dias L2 is a detected diastolic phase signal at said another wavelength.

20. A spectrophotometer as in claim 19, wherein said processing means converts said ratio R from a voltage reading to a reading in watts and adds watts of infrared energy emitted by said chopper wheel to determine a temperature difference between said internal temperature and said chopper wheel, thereby eliminating discontinuities in said ratio R.

21. A method of noninvasively measuring a concentration of at least one predetermined, constituent in a person'"'"'s blood, comprising the steps of:

detecting infrared emissions generated and emitted by a person;

detecting a temperature of said person at a point of emission of the infrared emissions detected in said infrared emissions detecting step;

determining infrared absorption of at least one predetermined constituent of a person'"'"'s blood using said infrared emissions detected in said infrared emissions detecting step;

determining the infrared emissions corresponding to said temperature measured in said temperature measuring step; and

calculating the concentration of said at least one predetermined constituent as a function of the infrared emissions detected in said infrared emissions detecting step and the determined infrared emissions determined in infrared emissions determining step.

22. A method as in claim 21, comprising the further step of synchronizing the detection of said infrared emissions with systolic and diastolic phases of a cardiac cycle of the person.

23. A method as in claim 21, wherein said calculating step comprises the step of calculating the concentration C of said at least one predetermined constituent in accordance with the equation:

space="preserve" listing-type="equation">I/I.sub.o =e.sup.--CLX,

where L is a pathlength from said point of infrared emissions to a detection point, X is an experimentally determined extinction coefficient, I is the detected infrared emissions, and I_o is the incident energy within said person at said point of emission, defined from Planck'"'"'s equation as;

##EQU7## where T_R is a transmission coefficient of a filter which passes said at least one predetermined constituent, ε

is emissivity of skin, C₁ =3.74×

10⁴, C₂ =1.438×

10⁴, T is the internal temperature of said person at said point of infrared emissions where said temperature is detected, and λ

is a wavelength of said filter.

24. A method of noninvasively measuring a concentration of at least one predetermined constituent in a person'"'"'s blood, comprising the steps of:

detecting infrared energy generated and emitted by the person in a wavelength range including n different wavelengths of at least 2.0 μ

m, said infrared energy containing energy at each of said n wavelengths which is differently absorbed by said at least one predetermined constituent whereby each predetermined constituent readily absorbs infrared energy at least one of said n wavelengths and minimally absorbs infrared energy at another of said n wavelengths, and outputting at least one detection signal representative of infrared energy at said n wavelengths which has been emitted by said person and selectively absorbed by said at least one predetermined constituent;

measuring an internal temperature of said person at a point where said infrared energy is detected in said detecting step;

determining the infrared emissions corresponding to said internal temperature measured in said temperature measuring step; and

calculating the concentration of said at least one predetermined constituent as a function of the infrared energy detected in said detecting step and the determined infrared emissions determined in infrared emissions determining step.

25. A method as in claim 24, comprising the further step of synchronizing the detection of said infrared energy emitted by the person with systolic and diastolic phases of a cardiac cycle of the person.

26. A method as in claim 25, wherein said synchronizing step includes the step of determining diastolic and systolic time intervals respectively occurring during the systolic and diastolic phases of the cardiac cycle of the person, whereby said detecting step is performed during said systolic and diastolic time intervals.

27. A method as in claim 24, wherein said calculating step comprises the step of calculating the concentration C of said at least one predetermined constituent in accordance with the equation:

space="preserve" listing-type="equation">I/I.sub.o =e.sup.--CLX,

where L is a pathlength from a point where said infrared energy is emitted to said point where said infrared energy is detected, X is an experimentally determined extinction coefficient, I is the infrared emissions detected in said infrared energy detecting step, and I_o is the incident energy within said person at said point where said infrared energy is emitted, defined from Planck'"'"'s equation as;

##EQU8## where T_R is a transmission coefficient of a filter which passes said at least one predetermined constituent, ε

is emissivity of skin, C₁ =3.74×

10⁴, C₂ =1.438×

10⁴, T is the internal temperature of said person at said point where said infrared energy is emitted, and λ

is a wavelength of said filter.

28. A method as in claim 24, wherein said concentration calculating step includes the step of forming a ratio R=(Sys L1-Dias L1)/(Sys L2-Dias L2), where Sys L1 is a detected systolic phase signal at said one wavelength, Dias L1 is a detected diastolic phase signal at said one wavelength, Sys L2 is a detected systolic phase signal at said another wavelength, and Dias L2 is a detected diastolic phase signal at said another wavelength.

29. A method as in claim 28, wherein said concentration calculating step includes the steps of converting said ratio R from a voltage reading to a reading in watts and adding watts of infrared energy emitted by a chopper wheel of an infrared emissions detector to determine a temperature difference between said internal temperature and said chopper wheel, thereby eliminating discontinuities in said ratio R.