NON-INVASIVE DEVICE AND METHOD FOR DETERMINING CONCENTRATIONS OF VARIOUS COMPONENTS OF BLOOD OR TISSUE

Abstract: A non-invasive device and method for continuously monitoring concentration levels of blood constituents utilizes a polychromatic light source that emits light over a broad spectrum of wavelenghts. The light is passed through, or reflected from, a part of the subject. That light is then separated into its various components by means of a grating, or prism, and the near infrared band is focussed onto a linear array detector. A microprocessor uses the output of the array detector to measure the light transmitted (T), calculate the absorbance (log 1/T) and calculate the second derivative of the absorbance. A calibration equation is used for each constituent to be monitored to convert the absorbance second derivative measurements to a concentration level for that constituent. The device is programmed to take measurements between heart beats and to adjust for the temperature of the sample being taken. The memory in the microprocessor can be used to assist with record keeping and with dosage calculations.

Description: NON-INVASIVE DEVICE AND METHOD FOR DETERMINING CONCENTRATIONS OF VARIOUS COMPONENTS OF BLOOD OR TISSUE FIELD OF THE INVENTION This invention relates to a non-invasive device and method for continuously monitoring and measuring concentration levels of blood constituents in humans or animals, using the near infrared portion of the light spectrum and, in particular, relates to a device suitable for continuously, or on demand monitoring concentration levels of blood contituents within the human body. DESCRIPTION OF THE PRIOR ART Previous devices for non-invasively monitoring concentrations of blood constituents of a patient are known. Usually, a sensor is used to externally measure either the concentration of the constituent in gases emitted by the body; or the concentration contained in perspiration; or the concentration contained in body fluids such as tears, saliva, or urine samples; or, alternatively, the blood constituent is measured using radiation passed through a part of the patient's body such as the earlobe. However, some of the previous radiation measuring devices, have a radiation source which emits light in one wavelength only and are therefore not accurate or broadly applicable enough for practical use. Other previous devices (eg pulse oxymetry) have more than one light source but have only a limited number (eg. three) of measuring wavelengths. In the US Robinson patent No. 4,975,581, there is described a non-invasive device using a broad¬ band lamp whose light, after passing through the test sample is optically coupled through a number of light filters, each with its own designated transmission, wavelength, to the collector. While the Robinson patent shows the use of several wavelengths at the source only a limited number of these wavelengths are collected and only some of those collected actually show differential absorption. Some of these previous devices (eg US Rosenthal patent No.4,286,327) must measure both the intensity changes in the range of transmission wavelength and the changes in intensity distribution. Further, some previous devices are controlled to take a series of measurements at successively higher or lower wavelengths. This can be extremely time consuming. Still further, some previous devices do not take into account changes in the thickness of one patient's earlobes (or other body part) compared to that of other patients or the change in size of a patient's earlobes (or other body part) and hence the transmission path length due to the pulsing of blood through the lobe (or other body part). Some prior devices do not take into account temperature variations in the earlobes (or other body part) from patient to patient or the results fluctuate with prolonged operation. Some previous devices do not address the problem of stability of placement of the body part in relation to the optical path of the instrument. It is equally important to control the physical distance between entry and exit points as it is allow free circulation of blood in the finger during the measurement process. Light which enters the body part selected is typically scattered, but to varying degrees in different individuals and to varying degrees at different times in the same individual. Allowances must be made for such scattering. Instrument ' s which are based on a single detector placed adjacent to the body part measure only a fraction of the light impinging on the body part. The fraction not measured is partly lost due to absorption and partly lost due to scattering. The part lost due to scattering is not accounted for and this results in errors in estimating the part accounted for by absorption. The farther the detector is located from the body part measured, the greater the error due to scattering unless some independent measurement is made. Previous devices are not sufficiently accurate to be used in the actual measurement of blood constituent concentration levels by patients; or, they are designed to measure for one component only and must be physically changed to measure for a different component; or, the device takes an unreasonably long time to produce a result; or, they cannot produce results in an easy-to-use form; or, they cannot measure the results of two or more components simultaneously; or they do not collect measurements at sufficient wavelengths to produce accurate results; or they do not average the results; or the results are not consistent enough when used with patients of widely varying characteristics. Obviously, if the device gives an inaccurate reading, disastrous results could occur for the patient using the device to calculate, for example, dosages for insulin administration. The fundamental requirement of non-invasive devices is that they produce accurate, reliable results with patients of widely varying characteristics so that they can replace invasive techniques. None of the prior art devices has met this requirement. Invasive techniques of measuring blood constituents are, of course, in common usage. These techniques are painful, potentially dangerous and expensive to operate. The normal procedure is to obtain a blood sample from a vein and this sample is then tested in a medical laboratory, using a number of chemical procedures to measure each constituent separately. Alternatively, home glucose testing uses a finger puncture that is spotted onto an enzyme-based semi-permeable membrane test strip and is allowed to react for a certain length of time with insulin administration, then based upon either a visual colour comparision with a standard colour chart or by means of a more accurate and unambiguous spectroscopic technique (for example reflectance) . There is a risk of infection and sometimes a patient can develop a rash when these invasive techniques are used. SUMMARY OF THE INVENTION It is an object of the present invention to provide a device for monitoring or measuring the concentration levels of one particular constituent or, alternatively, of measuring the concentration level of several different components simultaneously, said device producing results in a short time period that are highly accurate and compare favourably to invasive techniques. A non-invasive device for measuring concentration levels of blood and tissue constituents in living subjects uses a polychromatic light source emitting a broad spectrum of light wavelengths in the near infrared range. The light passes through a filter to limit the light to a range of approximately 650 nra to approximatelyl250nm. The light source is powered by a stabilized power source and said device has a receptor shaped so that part of said subject can be placed in contact with said receptor. The receptor also has means for eliminating extraneous light and has an entrance and exit for said light from said light source. A distance between the entrance and exit is constant. The receptor is located relative to said light source so that when part of said subject is properly placed in contact with said receptor, the light source can be activated and light from said light source within said range at several different wavelengths simultaneously is directed onto said part. There are means for collecting substantially all of said wavelengths of said light within said range at several different wavelengths simultaneously after said light has been directed onto said part. There are means for dispersing said collected light into component wavelengths of said collected light. There are means for measuring at least one of transmittance and reflectance of said collected light at several different wavelengths simultaneously. There are means for transforming siad measurements to enhance detection of at least one constituent from other constituents by using a calibration equaton for said at least one constituent. There are means for determining the concentration level of said at least one constituent and for producing a result for each concentration level determined. In a method for continuously monitoring concentration levels of blood constituents with a living subject such as humans or animals, there is used a polychromatic light source that emits a broad spectrum of light in the near infrared range from 650 nm to 2700nm. The method is characterized by passing said light through a filter to limit the light to a range from approximately 650 nm to appproxi ately 1250 nm, directing said light within said range at several different wavelengths simultaneously onto a part of said subject, collecting substantially all of said wavelengths of said light within said range after said light has been directed onto said part, collimating the collected light onto a grating, dispersing said light onto a linear array detector, said linear array detector taking measurements of at least one of transmittance and reflectance of said collected light in said near infrared range at several different wavelengths simultaneously, scanning said linear array detector and passing said measurements to a microprocessor, taking a reference set of measurements, transforming said measurements to enhance the detection of at least one constituent from other constituents by using a calibration equation for said at least one constituent, determining the concentration level of said at least one constituent of said blood and tissue and producing a result for each concentration level determined. BRIEF DESCRIPTION OF THE DRAWINGS In drawings which illustrate a preferred embodiment of the invention: Figure 1 is a schematic showing the basic components of a single beam device for non-invasively monitoring the concentration levels of blood constituents; Figure 2 is a schematic showing the basic components of a ' dual beam device for non-invasively continuously monitoring the concentration levels of blood constituents; and DETAILED DESCRIPTION OF A PREFERRED EMBODIMENT The near infrared region of the electromagnetic spectrum is generally considered to be the spectral range extending from 650 nm through to 2,700 nm. Absorption bands observed in this range are primarily the combination and overtone bands of the fundamental infrared bands. Although very weak in intensity, being typically less than one-tenth in intensity than those of the fundamental infrared bands, these bands are considered to be quite analytically useful because nearly all chemical species exhibit characteristic absorption bands in this spectral range. The near infrared region is particularly well suited to in vivo diagnostic applications because in human tissue there is adequate reduction in absorption of the incident radiation that penetration of the radiation through the tissue is sufficient to allow accurate quantitative analysis. As shown in Figure 1, a non-invasive single beam device for measuring concentration levels of blood constituents has a polychromatic light source. The light source can emit light over a very wide bandwidth including light in the near infrared spectrum. The light from said light source passes first through a filter which limits the energy of the light incident on the body part to a range of approximately 650 to approximately 1250 nm. Preferably, the filter limits the energy of the light incident on the body part to a range of approximately 700 nm to approximately llOOnm. The purpose of limiting the light is to eliminate the light rays that heat the finger, thereby allowing a higher intensity bulb to be used. With a higher intensity bulb, a measurement can be taken more quickly, thereby minimizing the opportunity for movement of the body part. After passing through said filter the near infrared radiation passes through a collimator, which is a lens that concentrates the light into a narrow parallel beam. Said parallel beam is focussed by a second lens on the entry port of the receptor. Said receptor is shaped to receive that part of the body, in this case, a finger. The light passes through the receptor and through the finger and is scattered by said finger. The collimated rays of said scattered light are collected by a third lens and directed through a slit to a fourth lens which collimates said light onto a diffraction or holograptiic grating. The light which passes through the grating is dispersed into its component wavelengths and focussed by lenses onto the linear array detector so that the light in the infrared region falls along the length of said detector. The light could be collected by reflective surfaces rather than lenses.Said linear array detector has a series of diodes (each diode representing one element) and is electronically scanned to measure the charge accumulated on each element. The detector can be photo diode array. The charge is proportional to the intensity of light falling on each element of said array and hence measures the intensity of light for each wavelength transmitted through or reflected from the tissue in the receptor. The detector is connected to the microprocessor through an analog to digital converter, with the microprocessor analysing the measurements and ultimately producing a result for each concentration level determined. The result can be shown on a display and/or printed on a printer. A keyboard allows a user to control the device, for example, to specify a particular constituent to be measured. After the measurements are taken for the transmittance and/or reflectance, the log of the inverse of these measurements is taken, that is, log (1/T) and log (1/R), where T and R represent the transmittance and reflectance respectively. For calculation of the absorbance [ ie. log (1/T) or log (1/R)], it is necessary to perform a reference measurement of the light incident on the body part. To do this, the lens which focuses and directs the near infrared light onto the receptor is removed. In the absence of said lens, collimated infrared light is directed into the entry port of the receptor. Since the light passing through the receptor in the absence of a body part is many times more intense than the scattered light collected from said body part, a neutral density filter is placed at the exit port of the receptor so that the intensity of dispersed light incident on the linear array detector does not drive said detector to saturation. The placement and displacement of said lens and neutral density filter are accomplished by attaching them to a common shaft and rotating the shaft with a motor. The linear array detector has several elements, preferably 256, and each element has a slightly different leakage current. To compensate for this leakage current with a predetermined integration time, it is necessary to perform the integration in the absence of light so that the effects of the leakage current can be subtracted. To accomplish this a shutter is placed immediately after the slit to block the light during the dark scans. If different integration t_ ?es are used for the measurement and reference scans, then dark current measurement must be performed for both integration times. Once the detector is enabled to integrate the light falling on its various elements, each said element begins to accumulate a charge proportional to the incident light. The rate at which the charge accumulates for each said element is proportional to the intensity of light falling on that element. The intensity of light falling on an element is dependent on the amount of scattering in the body part through which the light passes. The greater the degree of scattering, the less light is collected for the collimator which passes light on to the diffraction grating and thence on to the detector. To measure the degree of scattering it is only necessary to integrate for a long enough period of time for the analog to digital conversion (ADC) value for the wavelength at which the peak light throughput occurs to fall within a specified range of analog to digital conversion (ADC) values. This may be accomplished by starting with an arbitrary or average integration time. If the light throughput is so great as to saturate the detector at the chosen wavelength, the ADC value will be at a maximum, in which case the integration time is halved and another measurement is made. When the ADC value is less that the specified range (eg. 12000 to 14000 for a maximum value for the converter of 16384 or approximately 73% to approximately 85% of the maximum value) a calculation is made to determine the integration time necessary to place the ADC value within the specified range. A measurement is then made and the integration time and ADC value are saved to memory for that measurement. By dividing the obtained ADC value by the integration time (IT) and taking the log of the quotient, a value is obtained which has a strong relationship to the amount of scattering. This value, log (ADC/IT) , can then be used for multiplicative scatter correction or can be introduced as a variable in calculating the concentrations of analytes. For wavelength and absorbance calibration of the instrument, a shutter is inserted in the collimated beam preceding the finger receptor. This shutter positions a calibration filter (eg dydimium) so that well known absorbance peaks present in the filter can be routinely used to calibrate for wavelength and absorbance accuracy. The polychromatic light source can be a quartz-halogen or a tungsten halogen bulb and may be powered by a stabilized power source, for example, a DC power supply, or by a battery. It should be noted that, after activation of the light source, the scanning detector is read so that light is passed through the receptor and measured by the detector by taking a series of measurements on a selected wavelength. Measurements on this wavelength are sensitive to increased plethysmographic volume, or in other words, path length and so measure the heart pressure pulse. The microprocessor control activates the scanning of the linear array detector only after a detected pulse has occurred and the full spectrum measurements are then taken for the light after it passes through the receptor. Scanning is stopped when another pulse is detected on the selected wavelength. In other words, measurements are taken only when the blood pressure in the finger or ear or other part of the person is at a constant level. This ensures that the path length of the tissue through which the light passes will be uniform. In a further variation, the device can take measurements regardless of the pulse of the subject. The microprocessor can then be controlled by computer software to select those measurements that are taken between pulses and to base the calculation of the concentration levels on the selected measurements. In a still further variation, the measurement upon which the results are based could be taken during pulses. In relation to said pulse it is possible to collect data at the peak of said pulse as well as between said pulses. In this way the difference between the two measurements would be absorption attributable to blood constituents only. There are various means for detecting a pulse, for exampl, using plethysmographic blood pressure, sonograms or electrocardiograms. The receptor has means for eliminating extraneous light. For example, where a finger is the body part of a patient through which the light passes, the receptor has an oblong shape similar to, but larger than the shape of the finger. The means for eliminating extraneous light from the receptor is a flexible ring that surrounds an inner surface of an entrance to the receptor. When the finger is inserted, the flexible ring forms a seal around the finger. All surfaces within the device, including surfaces within the receptor, are made non-reflective to minimize stray light. Fibre optics can be use with the receptor to direct light from the source onto a body part and to collect the dispersed light from said body part for direction through the collimator to the diffraction grating and the detector. Also, the second derivative of the said measurement (ie.of the log of the inverse) may be taken in order to reduce any variation in the result that will be caused by a change in path length for the light. When the device is in use, various users will have fingers of different shape, colour and skin thickness depending on the person being tested and will produce differing degrees of scattering. The degree of scattering will produce differing effective pathlengths for the light in passing through the finger. The effect of the different path lengths and hence differing absorbances can be minimized by taking the second derivative of the measurement. The use of the second derivative calculation minimizes base line shifts due to different path lengths or absorbing water bands, and in addition, enhances the separation of overlapping absorption peaks of different constituents of the mixture being analyzed. The diffraction grating (which may be a holographic diffraction grating) is used to spatially spread the spectrum of the collected light onto the scanning detector. The scanning linear array detector is preferably a 256 element linear array. The detector collects substantially all of the wavelengths directed onto the body part but only a small portion of the light intensity directed onto the body part. The noise levels within the device are reduced by the multiple scanning technique whereby the scanner takes a number of measurements and then averages the results. For example, the scanner can scan the entire spectrum of interest two or three hundred times per second between heart beats and then average the results. Depending on the averaging technique used by the scanner and the number of readings taken, a reading can normally be obtained in le ; than two seconds. The device can be used to de »ιrmine the concentration of only one component of the sample in the receptor or several components derived from the same averaged spectra. Of course, a the number of components that are being measured increases, the time taken to display and/or print the results increases, due to computer processing time. However, the increased time is still less much less than two minutes. The time for taking measurements (a several different wavelengths simultaneously through many repetitions and then averaging the results) is usually approximately 3 minutes and is always less tha 5 minutes. The time depends on the number of repetitions and the number of constituents being analysed. Taking measurements quickly is particularly important when children are the subjects as they often find it very difficult to keep their finger stationary even for a brief period of time. Shown in Figure 2 are the basic elements of a dual beam equivalent of the foregoing instrument. There several important differences in the optical system for the dual beam instrument: 1) The reference beam is directed around the finger receptor through the use of four transmissive, but reflective surfaces. The amount of light reflected off the four surfaces is reduced so as to be equivalent t the attenuation provided by the neutral density filter of the single beam instrument 2) To provide collimated light for the reference beam, an additional lens is inserted to collimate the light which is focussed into the finger receptor. This arrangement makes it unnecessary to move the focussing lens as is requird with the single beam device. 3) In the dual beam instrument the only moving parts are the three shutters: a) a dual shutter to select measurement and reference scans; b) a shutter to block the light during the dark scans; and c) a shutter to insert a calibration filter during wavelength and absorbance calibration. An advantage of the dual beam instrument is that the reference scan can be taken without removing the finger from the receptor. The operation of the dual beam device is essentially the same as the single beam instrument except that two important advantages accrue from the dual beam arrangement: 1) Continuous measurement is possible; 2) If any drift in instrumentation occurs it can be offset by counterbalancing sequences of measurement and reference scans. For example, a sequence of measurement, reference, reference and measurement scans, when averaged together, would eliminate any linear drift occurring over the time of scanning. For either instrument, the calibration equation by which the blood glucose was computed was derived from a statistical fitting of the spectral data for a large number of subjects to the actual laboratory measured results for their blood glucose. While a best fit of spectral data is utilized to derive a calibration equation for each constituent desired to be measured, one type of best fit is a least squares best fit. The calibration results were cross validated using the spectral data for an independent sample of subjects. The particular wavelengths for absorbance were chosen to minimize the standard error of prediction (cross validation) . The equation so generated has the form of: Y = KO + Kl(Ai) +K2(Ai) +Kn(Ai) Where Y is the concentration of glucose K0,K1,K2, ....Kn are constants for n wavelengths Ai is the measured Absorbance or second derivative values of absorbance for ith wavelenths in nanometers (nm) corresponding to the Kn constants. The constants K0,K1,K2 and Kn are dependent upon the instrumentation including the optics and detectors and so must be determined independently for each instrument design. The results obtained can vary with the temperature of the sample or finger of the user. Therefore, the device contains a temperature sensor so that the temperature of the sample can be measured rapidly at the time of the spectral sampling. This temperature sensor is typically a small-mass thermocouple. Computer software can then be used to allow the microprocessor to compensate for spectrum deviations due to the temperature. So as not to delay the production of results, the temperature sensor has approximately a one hundred millisecond response time. The scanning detector is a photodiode array that is positioned to intercept, across its length, the dispersed spectrum from the diffraction grating. The microprocessor is directed by software to scan the scanning detector and calculate the absorbance spectrum and the second derivative of the spectrum. The microprocessor can then calculate the concentration of the particular components being measured using the absorbance and second derivative values for a number of selected wavelengths. The calibration equation used in each case is determined by the analyte being measured. The microprocessor can collect up to one hundred spectra in a period of one to two seconds and can then immediately calculate the second derivative of the averaged results. Preferably, the results will be digitally displayed for the user. Also, by using the memory capacity of the microprocessor, a user can monitor trends by comparing the most recent result with previous results. For glucose measurements, this will be of great assistance to a diabetic in order to enable the diabetic to determine future insulin dosage requirements. While examples noted above have been primarily related to measuring glucose concentrations, the device can be used to measure various other components found within human blood or tissue for example, cholesterol, alcohol, lactate, carbon dioxide, nitrogen, cortisol, creatine, creatinine, glycosolated hemoglobin, Catt, K t C1-, HCO3-, H P0 -, ketone bodies, lipids, fat, urea, amino acids, fatty acids and blood oxygenation levels to name a few. Devices for determining glucose levels can be pocket-sized and will be safer, more accurate when used by unskilled persons, less painful and much more convenient than invasive techniques presently being used. The same can be said for devices that measure cholesterol levels. As is well known, alcohol levels are presently measured by either taking a blood sample or a breath sample. Approved breathalyzers are extremely expensive and certain disposable parts must be used for sanitation purposes or are chemically "consumed" as part of the measurement. With the device of the present invention, alcohol levels can be measured quickly and easily without any active participation by the person whose alcohol level is being measured. The device could even be used when the person being measured was unconcious. Presently, in the field of sports medicine, the level of lactate present in muscles requires a biopsy and blood test. When athletes are in training for an upcoming event, biopsies are impossible because of the damage that they cause to the muscle. With the device of the present invention, lactate levels can be determined non-invasively. Since the second derivative is taken and with the multitude of wavelengths throughout the spectrum being available for analysis, it is possible to distinguish between various components simultaneously. For example, alcohol and glucose, which have presented problems in the prior art, can be distinguished. While the device of the present invention en be designed to measure one component, it is also possible to design a device to measure several components simultaneously. In fact, a primary application of the device will be for measuring 10-40 or more constituents that are now typically measured in a medical or hospital lab after a vial of blood is extracted from the patient or animal. Further, this multi-•constituent measurement can be completed and results displayed in seconds right in the doctors office rather than received in days or weeks as is. the practice today.

Claims: CLAIMS: 1. A non-invasive device for measuring concentration levels of constituents of blood and tissue in a living subject such as a human or animal, said device being characterized by a polychromatic light source that emits a broad spectrum of light in the near infrared range, said light passing through a filter to limit the light to a range from approximately 650 nm to approximately 1250nm, said light source being powered by a stabilized power source, said device having a receptor shaped so that part of said subject can be placed in contact with said receptor, said receptor having means for eliminating extraneous light, said receptor having an entrance and exit for said light from said light source, a distance between said entrance and exit being constant, said receptor being located relative to said light source so that when part of said subject is properly placed in contact with said receptor, said light source can be activated and light from said light source within said range at several different wavelengths simultaneously is directed onto said part, means for collecting substantially all of said wavelengths of said light within said range at several different wavelengths simultaneously after said light has been directed onto said part, means for dispersing said collected light into component wavelengths of said collected light, means for measuring at least one of transmittance and reflectance of said collected light at several different wavelengths simultaneously, means for transforming said measurements to enhance detection of at least one constituent from other constituents by using a calibration equation for said at least one constituent, means for determining the concentration level of said at least one constituent of said blood and for producing a result for each concentration level determined. 2. A device as claimed in Claim 1 wherein the calibration equation is derived from a best fit of spectral data obtained by said device to actual measured levels obtained coincidentally. 3. A device as claimed in Claim 2 wherein the means for transforming said measurements to enhance detection of at least one constituent from other constituents is to take the log of the inverse of at least one of the transmittance and reflectance of said collected light and further taking the second derivative of said log of the inverse. 4. A device as claimed in Claim 2 wherein the means for collecting is a linear array detector having an analog to digital converter connected thereto, said detector accumulating a charge with time, said charge being measured by an output to the converter, said means for measuring taking measurements when said charge has accumulated to a predetermined range, said range being close to a maximum value for the analog to digital converter. 5. A non-invasive device as claimed in any of Claims 1,3 or 4 wherein the filter limits the light to a range of approximately 700 nm to approximately llOOnm. 6. A device as claimed in any one of Claims 1, 2 or 4 wherein the means for measuring at least one of the transmittance and reflectance of said collected light at several different wavelengths simultaneously is a linear array detector and a microprocessor, said linear array detector receiving said dispersed light after the dispersed light has been directed onto said part and collected, said microprocessor causing said linear array detector to be scanned, said detector being connected to said microprocessor for taking said measurements. 7. A device as claimed in any one of Claims 1, 3 or 4 wherein the means for dispersing said collected light into component wavelengths of said collected light is a grating. 8. A device as claimed in any one of Claims 1, 3 or 4 wherein there are means for detecting a pulse withi -that part of the subject placed in contact with said receptor, there being means to control said device to use measurements taken immediately subsequent to the detection of a pulse and prior to a next pulse so that all measurements upon which a result is based are taken between pulses. 9. A device as claimed in any of Claims 1, 3 or 4 wherein there are means for detecting a pulse within that part of the subject placed in contact with said receptor, there being means to control said device to use measurements taken during a pulse so that all measurements upon which a result is based are taken during a pulse. 10. A device as claimed in Claim 2 wherein the device has a temperature sensor for measuring the temperature at that part of the subject located near the receptor with means for adjusting the measurements taken based on variations in said temperature. 11. A device as claimed in any one of Claims 1, 3 or 4 wherein said part of the subject is located within said receptor and light from which measurements are taken has been transmitted through said part. 12. A device as claimed in Claim 4 wherein the linear array detector has 256 elements. 13. A device as claimed in any one of Claims 1, 3 or 4 wherein the means for collecting said light at several different wavelengths simultaneously after said light has been directed onto said part are lenses. 14. A device as claimed in any one of Claims 1, 3 or 4 wherein there are means for detecting a pulse based on monitoring plethysmographic blood pressure. 15. A device as claimed in any one of Claims 1, 3 or 4 wherein there are means for detecting a pulse based on a sonogram. 16. A device as claimed in any one of Claims 1, 3 or 4 wherein there are means for detecting a pulse based on an electrocardiogram. 17. A device as claimed in any one of Claims 1, 3 or 4 wherein there is a collimator located between the polychromatic light source and said receptor so that light from the polychromatic light source passes through said collimator before passing into said receptor. 18. A device as claimed in any one of Claims 1, 3 or 4 wherein the means for collecting said light after it is directed onto said part is a lens, said lens being oriented and shaped to focus said light on a slit, said light passing through said slit to a second lens to collimate the light onto a diffraction grating, the means for measuring at least one of the transmittance and reflectance of said light being a linear array detector, said detector producing an output that is passed to a microprocessor which takes the measurements and is controlled by computer software to transform said measurements and determine the concentration level of at least one component of said mixture and produce a result. 19. A device as claimed in Claim 3 wherein the means for collecting is a linear detector having an analog to digital converter connected thereto, said detector accumulating a charge with time, said charge being measured by an output to the converter', said means for measuring taking measurements when said charge has accumulated to a predetermined range, said range being close to a maximum value for said converter. 20. A device as claimed in any one of Claims 4 or 19 wherein the measurements are taken when the charge is approximately 73% to approximately 85% of the maximum value for said converter. 21. A device as claimed in any one of Claims 1, 2 or 3 wherein the means for measuring at least one of the transmittance and reflectance of said collected light at several different wavelengths simultaneously is a linear array detector and a microprocessor, and there are means for reducing noise levels within said device by a scanning technique whereby the linear array detector scans the entire spectrum of interest many times per second for several repetitions ranging from approximately 8 to approximately 64 repetitions and the microprocessor then averages the results. 22. A device as claimed in any one of Claims 1, 3 or 4 wherein fibre optics is used to direct said light onto said part and to collect said light after said light is directed onto said part. 23. A device as claimed in any one of Claims 1, 3 or 4 wherein the means for collecting said light at several different wavelengths simultaneously are reflective surfaces. 24. A device as claimed in any one of Claims 1, 3 or 4 wherein the means for dispersing said collected light into component wavelengths of said collected light is a holographic diffraction grating. 25. A device as claimed in any one of Claims 1,3 or 4 wherein the receptor has dual beams so that reference measurements σn be taken while the part remaining in contact with the receptor. 26. A device as claimed in any one of Claims 1, 3 or 4 wherein the concentration level of constituents that are measured are selected from, but not limited to, the group of: amino acid, nitrogen, blood oxygenation, carbon dioxide, cortisol, creatine, creatinine, glucose, ketone bodies, lipids, fat, urea, amino acids, fatty acids, glyσosolated hemoglobin, cholesterol, alcohol, lactate, Ca++, K+, C1-, HCO β -, and HPO4-. 27. A device as claimed in Claim 25 wherein the linear array detector is a photo diode array and the means for dispersing said collected light into component wavelengths of said collected light is a grating, the light being collected from the grating by the photo diode array that is positioned to intercept the dispersed spectrum of light across its length. 28. A device as claimed in Claim 10 wherein the temperature sensor is a thermo-couple designed with a fast response time, of approximately 100 milliseconds, and there is a microprocessor to compensate for spectrum deviations due to temperature. 29. A device as claimed in any one of Claims 1, . or 4 wherein the means for measuring at least one of transmittance and reflectance of said collected light at several different wavelengths simultaneously is a linear array detector and a microprocessor and the measurement of several wavelengths simultaneously together with a speed of the microprocessor result in the time for taking a measurement and receiving a result ranging from three to five minutes depending on the number of constituents being analyzed. 30. A device as claimed in any one of Claims 1, . or 4 wherein there are means for transforming said mesurements to enhance detection of at least two constituents by using a calibration equation for each of said at least two constituents. 31. A non-invasive method for measuring concentration levels of blood and tissue constituents within a living subject such as a human or animal, using a polychromatic light source that emits a broad spectrum of light in the near infrared range from 650 nm to 2700 nm, said method being characterized by passing said light through a filter to limit the light to a range from approximately 650 nm to approximately 1250 nm, directing said light within said range at several different wavelengths simultaneously onto a part of said subject, collecting substantially all of said wavlengths of said light within said range at several different wavelengths simultaneously after said light has been directed onto said part, collimating the collected light onto a grating, dispersing said light onto a linear array detector, said linear array detector taking measurements of at least one of transmittance and reflectance of said collected light in said near infrared range at several different wavelengths simultaneously, scanning said linear array detector and passing said measurements to a microprocessor, taking a reference set of measurements, transforming said measurements to enhance the detection of at least one constituent from other constituents by using a calibration equation for said at least one constituent, determining the concentration level of at least one constituent of said blood and tissue and producing a result for each concentration level determined. 32. A method as claimed in Claim 31 wherein the measurements are transformed to enhance the detection of at least one constituent from other constituents by taking the log of the inverse of at least one of the transmittance and reflectance and further by calculating the second derivative of said log of said inverse. 33. A method as claimed in Claim 31 wherein there is an analog to digital converter connected to said detector, said detector accumulating a charge with time, said charge bein measured by an output to the converter said method including the step of having said means for measuring taking measurements when said charge has accumulated to a predetermined rangw within approximately 75% of a maximum charge for said detector. 34. A method as claimed in any one of Claims 31, 32 or 33 including the step of deriving the calibration equation from a best fit of spectral data obtained using the device to actual measured levels obtained coincidentally. 35. A method as claimed in Claim 32 wherein there is an analog to digital converter connected to said detector, said detector accumulating a charge with time, said charge being measured by an output to the converter, said method including the step of having said means for measuring taking measurements when said charge has accumulated to a predetermined range within 73% of a maximum value for said converter. 36. A method as claimed in Claim 35 including the steps of controlling the charge of the detector so that the accumulated charged is within a approximately 73% to approximately 85% of the maximum value for said converter when a measurement is taken. 37. A method as claimed in Claim 31 wherein the light from the light source is passed through a filter to limit the light to a range from approximately 700 nm. to approximately 1100 nm. 38. A method as claimed in any one of Claims 31, 32 or 33 wherein the means for measuring and collecting the light at several different wavelengths simultaneously is a linear array detector and a microprocessor, said method including the steps of scanning the detector using the microprocessor, taking several measurements in rapid succession and averaging the results with the microprocessor. 39. A method as claimed in any one of Claims 31, 32 or 33 wherein there are means for detecting a pulse within that part of the subject, the method including the step of controlling the device to take measurements between pulses. 40. A method as claimed in any one of Claims 31, 32 or 33 wherein there are means for detecting a pulse within said part of the subject, the method including the step of controlling the device to take measurements during a pulse. 41. A method as claimed in any one of Claims 31, 32 or 33 wherein there are means for detecting a pulse within said part of the subject with a microprocessor connected to said detector, said method including the steps of controlling the microprocessor to accept only those-measurements taken at the same time relative to said pulse. 42. A method as claimed in any one of Claims 31, 32 or 33 including the steps of controlling the microprocessor to scan the entire spectrum of interest many times per second for several repetitions ranging from approximately 8 to approximately 64 repetitions and having the microprocessor average the results.

Inventors: CADELL THEODORE E, CADELL, THEODORE, E.
Applicants: CADELL THEODORE E, CADELL, THEODORE, E.
Application year: 1992
Main classification: A61B5
IPC codes: A61B5, G01N21