OPTICAL METHOD AND DEVICE FOR DETERMINING BLOOD GLUCOSE LEVELS

Abstract: Blood glucose levels of a person are determined by a device (1) which provides a changing light pattern which changes in regard to one or several parameters defining its luminance, color, rate of flicker, spatial contrast, detail content, speed, or otherwise, provided that the change gradually stimulates one retinal system more than another retinal system. A person observes the changing light pattern until a subjective visual effect occurs, which is preferably an observer that perceives dramatic change in the appearance of the light pattern, for example, a change in the perceived direction of rotation. The subjective visual effect indicates a specific ration of stimulation of the two retinal systems, for example, the point of balanced stimulation of the two systems. Upon noting the subjective visual effect, the patient actuates a mechanism (4, 5) which parameter values with a corresponding blood glucose level using predetermined calibration data. Thereby, the person's glucose level is accurately determined in a completely non-invasive manner.

Description: OPTICAL METHOD AND DEVICE FOR DETERMINING BLOOD GLUCOSE LEVELS Field Of The Invention This invention relates generally to the field of optics and more specifically to a method and device for analyzing a patient's perception of a changing light pattern and relating such to the patient's blood glucose level. Background of the Invention More than ten million people in the United States of America suffer from diabetes, a deficiency in the body's ability to regulate blood glucose levels . Individuals afflicted with the disease must control their blood glucose levels by measuring their blood glucose levels as frequently as possible and planning accordingly their food intake, level of physical activity and insulin dosage. The measurement of blood glucose levels is done using one of several available invasive techniques. Invasive techniques require withdrawal of a blood sample from the patient each time an analysis is to be performed. An accurate laboratory blood analysis requires withdrawing from 5 to 10 ml of blood and analyzing it using a laboratory instrument designed for performing such a biochemical analysis. However, the results of the test often are not available for several hours, and sometimes days. In addition, the instruments necessary to perform such an analysis are expensive and require that the blood samples be taken and analyzed by trained technicians. Another invasive technique, referred to as a "finger poke" or a "finger stick" uses an integrated, self-contained instrument that evaluates a much smaller blood sample (approximately 0.25 ml) . The small blood sample is obtained by puncturing a finger with a small lancet. The sample is then placed on a chemically treated carrier and inserted into the instrument . The finger poke devices normally provide the glucose concentration results in a few moments . However, they are still quite costly for private use. More recently, portable finger poke instruments have become available which require the use of single use, disposable, chemically treated carrier "strips". Although the portable instruments have a relatively low cost (about $100 to $300) , cumulative cost to diabetics for the normal supply of disposable carrier "strips" is considerable. Invasive techniques for glucose analysis are problematic and suffer from poor compliance. Although diabetics can forestall the debilitating and often fatal complications of diabetes by frequent monitoring and control, only a small fraction of diabetics monitor regularly their glucose levels. Diabetics find the current invasive methods of blood glucose monitoring painful, inconvenient and costly. To encourage frequent monitoring and control there is a clear need for a glucose monitor that requires no blood samples, is easy and convenient to use, is portable, and costs less than current methods. Non-invasive methods for measuring blood glucose have been described. However, to date none of these techniques has resulted in a commercially useful instrument. The non-invasive monitoring methods are roughly divided into measurements based on either (1) the intensity of light being transmitted through or reflected from the tissue ("intensity-sensitive" measurements), (2) the phase shift of modulated light transmitted through the tissue ("phase-sensitive" measurement) or (3) devices which use reverse iontophoretic means to remove substances through the skin as per U.S. Patent 5,279,543 issued January 18, 1994. When light is transmitted through perfused tissue in vivo, e.g., through a patient's finger, it is differently absorbed by the various components illuminated, namely blood, with its many constituent parts, tissue (including protein, fat, water, cholesterol, etc.), cartilage, and bone. Each component has a specific absorption spectrum, which indicates the absorption at each wavelength of light . The known intensity sensing methods for measuring the level of a blood constituent, including glucose, are based on measuring an absorption spectrum for blood perfused tissue at two or more different wavelengths, and subtracting therefrom the statistical absorption spectra for each of the various components, except for the one component being measured. It is assumed that after such subtraction, the remainder is the spectrum of the constituent to be measured. Rosenthal, et al . , U.S. Patent No. 5,086,229 refers to such a non-invasive, near-infrared quantitative analysis instrument for measuring blood glucose. The instrument contains a plurality of near-infrared laser sources having different wavelengths of emission and one or a plurality of photodetectors. A blood-containing body part, e.g., a finger, is placed between the laser sources and photodetectors . The light sources illuminate the body part and the wavelengths transmitted through the body part are detected. The absorption spectra obtained from the photodetector signals are compared with individual statistical absorption spectra of each constituent, which are stored in the memory of the instrument. A glucose level is derived from the comparison. The non-invasive phase sensitive measurement methods possess significantly higher sensitivity and a much higher signal-to-noise ratio than intensity-measurement methods. The higher sensitivity is the consequence of the noise sources affecting the amplitude, but not the phase, of a signal. In phase sensitive techniques, an instrument compares a known reference signal, e.g., a sine wave, with a measurement signal that has been passed through the tissue. The measurement signal will have a phase shift relative to the reference signal, and concentrations of blood constituents may be obtained from a measurement of the phase shift. Cote, et al. , "Noninvasive Optical Polarimetric Glucose Sensing Using A True Phase Measurement Technique," IEEE Transactions of Biomedical Engineering, Vol. 39, No. 7, July 1992, pp. 752-756, refers to passing linearly-polarized light through the anterior chamber of an excised human eye and determining the glucose level of the aqueous eye humor based on the phase shift between the reference signal and the measurement signal that was affected by glucose. A helium-neon laser beam, coupled through a rotating linear polarizer along with two stationary linear polarizers and two detectors, is used to produce reference and measurement signal outputs. The amplitudes of these outputs varied sinusoidally with a frequency twice that of the angular velocity of the rotating polarizer. The phase difference of the outputs would be proportional to the polarization rotation introduced in the measurement beam by the anterior chamber of the eye. Due to problems with both types of systems there is a continuing need for improved non-invasive analytical instruments and methods that would provide essentially the same accuracy as conventional invasive blood glucose tests. There also is a need for non-invasive, low-cost methods and instruments for the measurement of glucose levels in diabetic patients. There also is a need for a durable, cost-effective, and environmentally conscious nondisposable apparatus for measuring blood glucose. In view of such the present invention now provides an apparatus for non-invasive measurement of blood glucose concentration. Summary Of The Invention A human subject is presented with a changing light stimulus or pattern in which one or several parameters, for example the luminance, color, flicker frequency, spatial contrast, speed, etc., of a portion of the pattern or of the whole of the pattern, gradually change in a manner which stimulates a first retinal system (e.g., the P-system) and a second retinal system (e.g., the M-system) in a continuously changing ratio. The stimulus or pattern is observed until the person observing the pattern subjectively notes a specific change in the appearance of the light pattern, for example the appearance of a specific color in the light pattern, or the reversal in the direction of rotation of the light pattern. The specific change is associated with a specific ratio of stimulation of the M- and P-systems, for example the point of balanced stimulation of the two systems, or M-P crossover point. The value of at least one of the variable light stimulus parameters at the moment of occurrence of the specific change in appearance of the light stimulus, can be calibrated to the subject's blood glucose level via prior measurements of the subject's blood glucose level. Such value of the variable stimulus parameter when the specific change in the stimulus appearance occurs, will shift for any given person as the glucose level of the person changes, because the sensitivity of the two retinal systems change relative to each other in response to changes in blood glucose level. In one preferred embodiment, a series of images resembling windmill wheels are presented to a person in a manner which causes the person to perceive rotation of the wheel. A gradual change in the brightness or color of portions of the images or their background is then effected in such a manner that the series of images stimulates one retinal system (M or P) over time at a certain rate, and the other retinal system (P or M) at a different rate. The different manner in which the M- and P-systems respond to changes in the parameters of a light pattern make it possible to stimulate the M- and P-systems at different rates by varying continuously one or several parameters in the light pattern. The resultant ratio of stimulation of the two systems changes gradually over time. This gradual change in the ratio of stimulation of the two retinal systems is continued until the patient notes a reversal in the direction of apparent rotation of the wheel -- rotation reversal indicating a balanced stimulation of the M- and P-systems, or M-P crossover point. A change in blood glucose level affects the retinal systems in a manner which causes the M-P crossover point to shift in a predictable and consistent manner, because the sensitivity of each of the two retinal systems is affected differently relative to each other by changing blood glucose levels . The value of the variable parameter or parameters of the light stimulus at the point when the person notices the rotation reversal is directly related to blood glucose levels. Thus, by relying on the differential response of the M- system and the P-system to changes in certain types of light patterns, and on the differential change in sensitivity of the M- system and the P-system with blood glucose levels, the device and method provide an accurate, convenient, non-invasive means of measuring a patient's blood glucose level. An object of the invention is to provide a non-invasive optical means of determining a patient's blood glucose level . Another object is to provide the non-invasive means for determining glucose levels by using images or light patterns which provide visual stimulation to the retina and determining with such images or light patterns changes that take place in a patient's retina in response to changes in blood glucose levels . Another object of the invention is to provide a device which creates a changing light stimulus which when observed reaches an M-P crossover point which is related to the blood glucose level of the observer. Another object is to provide such a device which gradually stimulates one retinal system more and more and another retinal system less and less and provides for an actuation means which upon actuation records a point which can be related to the relative stimulation of each system which information can be related to the blood glucose level of the patient. Yet another object of the invention is to provide a device which provides a light stimulus with an observable M-P crossover point which device is calibrated with an established relationship between known blood glucose levels and measured M-P crossover points. A feature of the invention is that it uses changing light patterns. An advantage of the invention is that it is a non-invasive method of determining a blood glucose level. Another feature of the invention is that it capitalizes on the different sensitivities of the M-system and the P-system to determine information on blood glucose level. Another advantage is that the method can be quickly carried out in only a few seconds. Another advantage is that the device for measuring glucose levels via optical means can be inexpensively manufactured. Another advantage of the device of the invention is that the patient can reuse the device a plurality of times, i.e., it is not a one use disposable item and does require the use of any disposable components. Still another advantage is that the device is small (less than 10 cm in any dimension) light weight (less than 0.5 kg) and thus may be conveniently carried and used by an individual on an out¬ patient basis . These and other objects, advantages and features of the present invention will become apparent to those persons skilled in the art upon reading the details of the structure, methodology and usage as more fully set forth below with reference being made to the accompanying figures forming a part hereof. Brief Description Of The Drawings Figure 1 is a graph which conceptually shows the relative sensitivities of the M- and P-retinal systems at different glucose levels; Figure 2 is a schematic block diagram of an aspect of the invention; Figure 3 is a graph which conceptually shows how the M-P crossover point changes as blood glucose level changes; Figure 4 is a schematic view of the arrangement of components and the viewer being tested in a particular embodiment of the invention; Figure 5 is a graph relating flicker frequency to time; Figure 6 is a graph relating glucose level to time; Figure 7 is a graph relating glucose level to time; Figure 8 is a graph relating glucose level to time; Figure 9 is a graph relating glucose level to time; Figure 10 is a graph relating critical flicker period to time- Figure 11 is a black and white schematic view of a windmill light stimulus in a first position; Figure 12 is a black and white schematic view of a windmill light stimulus in a second position; Figure 13 is a graph relating background luminance at the point of rotation reversal of the windmill light stimulus to time; Figure 14 shows an embodiment of the device; Figure 15 is a schematic block diagram showing principal functional sections of the device of Figure 14; Figure 16 is a schematic flow diagram showing steps of a diagnostic sequence; and Figure 17 is a graph demonstrating how reaction time is compensated for. Detailed Description Of The Invention Before the present optical method and device for determining blood glucose levels is described, it is to be understood that this invention is not limited to the particular process steps, light changing, light stimulus or other steps and components described as such may, of course, vary. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting since the scope of the present invention will be limited only by the appended claims. It must be noted that as used in this specification and the appended claims, the singular forms "a", "an" and "the" include plural reference unless the context clearly dictates. Thus, for example, reference to "a changing light stimulus" refers to one or more changing light stimuli, reference to "an actuation means" refers to one or more means and so forth. Unless defined otherwise all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in art to which this invention belongs. Although methods and materials similar or equivalent to those described herein can be used in the practice or testing of the present invention, the preferred methods and materials are now described. All publications mentioned hereunder are incorporated herein by reference. The publications discussed herein are provided solely for their disclosure prior to the filing date of the present application. Nothing herein is to be construed as an admission that the invention claimed herein is not entitled to antedate such publications by virtue of prior invention. Definitions The term "appearance of colors" is used to describe a subjective visual effect occurring at a specific frequency when the retina is stimulated with a flickered light of variable frequency. For example, the appearance of colors can consist of pink and green irregular patches that appear to radiate from the point of fixation. The term "cessation of radial movement" is used to describe a subjective visual effect occurring at a specific frequency when the retina is stimulated with a flickered light of variable frequency. For example, at lower frequencies, faint shadows like concentric ripples in water radiate from the point of fixation towards the periphery, while at higher frequencies, the shadows travel in the opposite direction. At an intermediate frequency, the radial movement of the shadows ceases momentarily before changing direction; this is the frequency of cessation of radial movement and is an example of a subjective visual effect occurring during the observation of a changing light pattern. The term "changing light pattern" is intended to mean a light pattern that changes over time with respect to one or several of its defining parameters, for example its luminance, color, shape, size or rate of flicker. The term "changing parameter" shall mean any parameter that changes during the presentation of a light pattern, in order to provide a changing stimulation to the observer's retina. For example, a changing parameter in the windmill light pattern may be the luminance of the background, which could increase gradually. In a flickered stimulus, the flicker frequency may increase, or the length of the ON periods may increase over time. The term "continuously increasing ratio" is used to describe the ratio of stimulation of one retinal system over the other, when such ratio increases continuously. Thus, if the sensitivity of the M- and P-systems change as shown in Figure 1, and if the light stimulus is assumed to change from left to right along the horizontal axis, the ratio of M to P stimulation in Figure 1 increases continuously from left to right, starting with a value of less than 1 on the left end of the diagram, reaching a value of 1 at the M-P crossover point, and continuing to increase to values greater than 1 towards the right side of the diagram. The term "critical parameter value" is used to describe the value of a variable parameter in a changing light pattern, at the point when the subject notices the subjective visual effect. The term "grid pattern" is used to describe a subjective visual effect occurring at a specific frequency when the retina is stimulated with a flickered light of variable frequency. The effect consists of a regular pattern, which some observers describe as a fine square grid, and others as a fine honeycomb pattern. The terms "light pattern", "light stimulus" and the like are used interchangeably herein and are intended to mean any arrangement of light-emitting surfaces that can be used to stimulate the retina. A light pattern can be specified by three kinds of properties: spectral properties (the color of each component part) , spatial properties (the size, shape and location of each part) , and temporal properties (how each part changes with time) . Examples of light patterns are a flickering light or a sequence of windmill images that appear to rotate. A light pattern can be produced with a variety of light sources, such as a CRT screen, an LCD screen, LEDs, fluorescent or incandescent sources, arc or gas discharge lamps, flash tubes, or natural sun light. In order to stimulate the retina with a light pattern the observer may look at the actual light source or the observer may look at an object that in itself is not ligh -emitting, but receives the light from a light source and re-directs this light to the eye of the observer by either reflection, scatter, diffusion or refraction. Appropriate filters and time-control devices can be used to give the desired spectral and temporal properties to the light pattern. The term "light pattern parameters" is intended to mean the set of parameters that define a light pattern at one moment in time. Light pattern parameters define the light pattern along three dimensions: spectral parameters, spatial parameters and temporal parameters. Examples of light pattern parameters are color, luminance, size, and rate of flicker. The term "luminance" shall mean the quantitative measure of brightness of a light source or an illuminated surface, formally defined as luminous flux per unit solid angle emitted per unit projected area of surface. The terms "M-retinal system", "M-system" , "P-retinal system" and "P-system" are used herein to describe the two complementary components of the visual system, presently regarded in vision science as the main channels for processing visual information. The M- and P- retinal systems originate at the ganglion cell layer of the retina and connect respectively to the magnocellular and parvocellular layers of the lateral geniculate nucleus in the brain. The M- and P- systems differ in their color selectivity, contrast sensitivity, temporal properties, spatial resolution and sensitivity to changes in blood glucose levels. The two systems are compared in Tables 1 and 2. It is understood that the differences with respect to some parameters may be gradual even though Tables 1 and 2 appear to imply a discrete and complete separation of sensitivities. The present invention makes use of the differences in the M- and P-systems to stimulate the two systems selectively and to gradually shift the stimulation from predominantly M to predominantly P or vice versa. The terms "M-P crossover point", "crossover point" and the like are used interchangeably herein to define the point where the M- and P-systems are stimulated substantially equally. The M-P crossover point can be reached by changing the light pattern gradually in such a manner that the light pattern first stimulates one system more than the other and then gradually changes the relative stimulation of the systems until both systems are stimulated substantially equally. When the crossover point is reached the two systems compete in conveying perceptual information about the stimulus, a point that is often accompanied by the appearance of a subjective visual effect. The subjective visual effect results from the sudden change of channel that carries the dominant information regarding the visual stimulus. Away from the crossover point, the system that receives greater stimulation dominates the perception of the stimulus. The M-P crossover point is used in this invention to measure changes in sensitivity of the M system, which are caused by shifts in blood glucose levels. Changes in M system sensitivity translate into shifts in the M-P crossover point, as explained conceptually in Figure 1. Thus by measuring shifts in the M-P crossover point, one can indirectly measure changes in sensitivity of the M system and thus changes in blood glucose levels. The term "perceived characteristic" is used to describe a subjectively perceived property or quality in a light stimulus or pattern, such as the perception of colors in a light flickering at a certain constant frequency near 25 Hz, or the perception of apparent rotation in a sequence of images resembling a windmill pattern with constant color, luminance and background. The perceived characteristic arises from the simultaneous stimulation of several retinal mechanisms that have different sensitivity to the light stimulus, which results in competition or interference between the mechanisms involved. The term perceived characteristic is used for a perceived quality in a light pattern that is not changing over time, whereas the term subjective visual effect, defined below, is used for a perceived quality in a light pattern that is changing over time. The term "ratio of stimulation of M and P systems" is used to describe the amount of stimulation of one retinal system relative to the other, or equivalently the ratio between the degree of stimulation of one system and the degree of stimulation of the other. When a light stimulus changes gradually, it may first stimulate preferentially the M-system, while stimulating the P-system only a small amount. As the stimulus changes, it may stimulate the M-system less and less and the P-system more and more, in which case we say that the ratio of M-system stimulation over P-system stimulation is decreasing. This case is illustrated in Figure 1. However, the ratio of stimulation can also decrease in a variety of other ways, for example if the M-system is stimulated less and less while the P- system is stimulated in a constant amount, or also less and less but at a slower rate of change than the rate at which the stimulation of the M-system is changing. The term "retinal system" is used to describe any of the functional components of the visual system, which components are distinguished from each other by their differential sensitivity to light stimuli. Vision scientists assume that the visual system in higher mammals is organized as a group of parallel systems, each containing neurons that have distinctive physiological properties and which analyze different aspects of the retinal image. These systems, also called pathways, channels, or mechanisms are organized as complementary pairs e.g., cone and rod, ON and OFF, X and Y, chromatic and achromatic, pattern and movement, sustained and transient, tonic and phasic, M and P. Some of these system pairs overlap -- for example, the tonic and phasic pair of systems seem to correspond to the X and Y pair, to the P and M pair and to the chromatic and achromatic pair. The segregation of visual processing into pairs of systems starts at the retina and continues into the lateral geniculate nucleus and higher visual centers of the brain. The term "subjective visual effect" refers to a sudden and dramatic change in the perceived quality of a gradually changing light pattern, or the sudden appearance of a quality or characteristic in the light pattern that was not present before. An example is the appearance of patches of color at a specific flicker frequency, when the light stimulus is a uniform white surface illuminated with a white light flickering at increasing frequency and observed through a red filter. Another example is the sudden reversal in the perceived direction of rotation of a sequence of windmill images in which the luminance of a set of vanes changes gradually. The changing parameter in these examples changes at such a slow rate that the observer does not perceive the parameter change in itself . The sudden change in perceived quality is a dramatic discontinuity in the appearance of the light pattern and is indicative of a new mechanism taking over the perception of the stimulus. The term "visual system" is used to describe the post- optical, or neural portion of the human visual system. In this definition, the visual system starts at the retina and includes the change such as the appearance of color patches, the appearance of a grid pattern, or the perception of radial movement stopping, starting, or reversing direction. It should be noted that such visual effects are perceived effects in that the color patches or the grid pattern were not present m the stimulus at all, but the stimulus was a uniform, featureless field of a constant color. Another subjective visual effect which might be noted is the reversal in the direction of rotation of a light pattern This pattern may not be rotating at all but rather presenting a series of images that creates the impression or appearance of rotation That apparent rotation may then reverse direction and the light pattern may then appear to rotate m the opposite direction when the stimulation passes over the M-P crossover point, as will be explained in greater detail in the Example 2 section A block diagram of the basic principles of the present invention is shown n Figure 2. Specifically, Figure 2 shows that a light stimulus is provided which light stimulus provides a variable parameter, e.g., a continually increasing rate of light flicker. This light stimulus is presented to the visual system which includes the P-system and the M-system The M-system is affected by glucose levels substantially more than the P-system The subjective visual effect determines that the crossover point has been reached and this allows the value of the variable parameter at crossover to be measured By relating the variable parameter values at crossover with glucose levels measured by conventional means the device can be calibrated A relationship is established between the M-P crossover value and the blood glucose level as is shown within Figure 3 The diagram shown within Figure 3 is shown only for illustration purposes, and it does not imply that the relationship follows a straight line. Clinical tests will determine the actual characteristic of this relationship When the patient activates the device indicating that the crossover point has occurred the microprocessor relates the parameters defining the light stimulus at that moment to the corresponding blood glucose level previously stored, thereby providing the patient with information on current glucose levels m a non-invasive manner Physiological Basis The operability ,of the device and method of the present invention s not dependent on the following explanation with respect to how the invention works However, the following information is given m order to provide those skilled in the art with an explanation on how the invention works l e , the underlying physiological events which make it possible for the device and method to determine glucose levels in the blood which enters the retina. The explanation is based on currently available theories and knowledge about the operation of the retina and the visual system. However, these theories and knowledge may change over time without affecting the operability of the device and method of the present invention. It is well understood that glucose is present in blood and can migrate to all tissues via the circulatory system. In particular glucose is an important metabolite for the retina. The retina possesses a high rate of metabolic and electrical activity which is almost exclusively fueled via the oxidative breakdown of glucose (Noell, W.K. 1959, The Visual Cell: "Electric and Metabolic Manifestation of its Life Processes," Am. J. Physiol . 48 :347,- Winkler, B.S. 1975, "Dependence of Rat and Rabbit Photoreceptor Potentials Upon Metabolism in vi tro, " Exp . Eye Res . 21:545) . The retina obtains the required glucose from an abundant blood supply provided to the retina via the choroid capillaries. Not only does the retina utilize glucose for its metabolic and electrical activity, but the retina is able to consume glucose in proportion to the amount of glucose available over a wide range of glucose levels (Ames III A., and Gurian, B.S. 1963, "Effects of Glucose and Oxygen Deprivation on Function of Isolated Mammalian Retina," J. Neurophysiol . 26 :617 ,- Winkler, B.S. 1972, "The Electroretinogram of the Isolated Rat Retina," Vision Res . 12:1183; Winkler, B.S. 1981 "Glycolytic and Oxidative Metabolism in Relation to retinal Function, " J. Gen. Physiol . 77 :667) . In view of the above it can be anticipated that changes in the blood glucose concentration will have noticeable effects on the visual system. Such effects have been demonstrated by others in areas unrelated to the subject of this invention. Specifically, glucose concentration affects rod-mediated responses in the perfused cat eye (Macaluso, C, Onoe, S. and Niemeyer, G. 1991, "Discrete Changes in Glucose Level Affect Rod- but not Cone-function in the Perfused Cat Eye," Invest. Ophthalmol . & Visual Science, Supplement 3_2:903) ; high blood glucose concentration decreases the detection thresholds with respect to low-contrast gratings and increases the ERG amplitude in humans (Barlow, R.B. Jr., Boudreau, E.A. and Pelli, D.G. 1993, "Metabolic Modulation of Human Visual Sensitivity," Tnvest. Ophthalmol . & Visual Science, Supplemen t 3_4.:785) ; and lastly, low blood glucose concentrations increase dark-adapted detection thresholds in humans (McFarland, R.A. and Forbes, W.H. 1940, "The TABLE 1 RETINAL M- AND P-SYSTEMS COMPARED M P Sensitivity to blood glucose levels High Low Sensitivity to fast flicker High Low Sensitivity at low light levels High Low Sensitivity to low-contrast patterns High Low Sensitivity to steady light Low High Sensitivity to color Low High Sensitivity to fine detail Low High Sensitivity to high-contrast patterns Low High Additional parameters which can be used to distinguish the M-system from the P-system are provided below in Table 2. Evolutionary age Conduction velocity Spatial integration Cell size Fluctuations in glucose level affect visual function in general and in particular by having a greater effect on the sensitivity of the M-system with no or a substantially smaller effect on the P-system. This conclusion has been reached via experimental results shown herein, which are discussed in detail in the Example 1 and Example 2 sections and summarized in Figures 6 - 10. Such experimental results are consistent with the work of others cited earlier in this section who have reported an effect of glucose levels on visual function. Specifically, Macaluso et al, (Macaluso C, Onoe S. and Niemeyer G. 1991, "Discrete Changes in Glucose Level Affect Rod- but not Cone-function in the Perfused Cat Eye," Invest. Ophthalmol . & Visual Science, Supplement 3_2_:903), found that the rod responses are affected by changes in glucose concentration, whereas cone responses are not. Similarly in humans, McFarland et al. , (McFarland, R.A. and Forbes, W.H. 1940, "The Effects of Variations in the Concentration of Oxygen and of Glucose on Dark Adaptation, " J. Gen . Physiol . 2_4:69) found that that the sensitivity of rod vision, but not that of cone vision, changes with variations in glucose level . It is known through the work of others that rod responses are carried only or primarily by the M-system, whereas the P-system carries only or primarily cone responses (Purpura K. , Kaplan E., Shapley R.M. 1988, Background Light and the Contrast Gain of Primate P- and M-Retinal Ganglion Cells, Proc . Natl . Acad. Sci . USA 85 =4534) . Thus, even though neither Macaluso et al . nor McFarland et al. mention any connection between their results and the M- and P- systems, their results are consistent with the conclusion that changes in glucose level affect the sensitivity of the M-system and not that of the P-system, and furthermore, that the direction of this effect is such that higher glucose levels cause an increased sensitivity in the M-system. Additional support for this conclusion comes from the work of Barlow et al, also cited earlier in connection with glucose levels affecting visual function (Barlow, R.B. Jr., Boudreau, E.A. and Pelli, D.G. 1993, "Metabolic Modulation of Human Visual Sensitivity," Invest. Ophthalmol . & Visual Science, Supplement 34 . :785) . These authors found that higher glucose levels increase the ability of human observers to detect low contrast patterns. Again, these authors did not connect this finding with the M- or P-systems, but it is known from the work of others that patterns of low contrast are preferentially detected by the M-system (Shapley, R. 1990, "Visual Sensitivity and Parallel Retinocortical Channels," Annu. .Rev. Psychol . 4.1:635-58) . Thus the results of Barlow et al are also consistent with the conclusion that increases in glucose level affect preferentially the M-system relative to the P-system by raising the sensitivity of the M-system. In summary, the experiments reported later in this patent and summarized in Figures 6 - 10, show that increases in blood glucose level raise the sensitivity of the M- system more than that of the P-system. This conclusion, although not stated explicitly in any prior report, receives support from the above cited reports, when one interprets those reports in terms of known properties of the M- and P-systems. This conclusion is an important part of the physiological explanation of how the present invention operates. To further explain the physiological basis of the present invention we next state some additional properties of the M- and P-systems. The M-system and the P-system have complementary specializations. More specifically they respond inversely to several parameters of a light stimulus as indicated in Table 1. For example the M-system is insensitive to color and most sensitive to fast flicker as well as coarse and low-contrast patterns while operating at low light levels. However, the P-system is sensitive to color and most sensitive to slow flicker and to patterns with fine detail and high contrast while functioning best at high light levels (Kaplan, E., et al . 1988, "Color and Luminace Contrast as Tools for Probing the Primate Retina," Weuroscience J?eε. Suppl . 8_ : S151 ; Schiller, P.H. and Logothetis, N.K. 1990, "The Color-opponent and Broad-band Channels of the Primate Visual System, " Trends in Neuroscienceε 13.:392; Kaplan, E., Lee, B.B. and Shapley, R.M. (1990) "New Views of Primate Retinal Function," In Progress in Retinal Research . N.N. Osborne and G.J. Chader, editors. Pergamon Press, Oxford, pp 275- 330) . As explained below, this complementary specialization of the M- and P-systems along with the selective effect of glucose levels on the M-system sensitivity are two facts that help explain how the present invention derives blood glucose information from the subjective response to a light stimulus. Determining Glucose Levels The complementary nature of the sensitivity of the M- and P- systems to light stimuli makes it possible to design a changing light stimulus or pattern that simulates the two systems in sequence, in other words, a light stimulus or pattern that first stimulates preferentially the M-system and later the P-system, or vice versa. This is accomplished by varying continuously a light pattern parameter that elicits complementary or contrary responses in the M- and P-systems. The variable parameter in the light pattern can be any of a variety of different parameters. For example, it is possible to continually and gradually change one or more parts of a light stimulus or pattern with respect to their color, luminance level, contrast, shape, size, detail content, texture, speed of movement, direction of movement including rotation, or rate of flicker. For example, light flickered at low frequency (e.g., 10 Hz) stimulates the P-system to a large extent and the M-system to a small extent. As the frequency increases, the flickered light stimulates the P-system less and less and the M-system more and more, until at high frequency (e.g., 40 Hz), the flickered light stimulates predominantly the M-system. In this example the variable frequency of the flickered light is a variable parameter in the changing light pattern. Near the middle of this range of frequencies (near 20-25 Hz), the sweep of flicker frequencies passes through a point -- the M-P crossover point -- where the M- and the P-systems are stimulated about equally. The term M-P crossover point denotes a theoretical point of balanced stimulation of the M- and P-systems, and since it is not possible to measure objectively the degree of stimulation of the M- and P-systems in a human observer, the M-P crossover point cannot be determined objectively. However, it can be measured subjectively, thanks to the fact that the crossing of the M-P crossover point is frequently accompanied by a sudden and dramatic change in appearance of the light stimulus -- a subjective visual effect. This visual effect results from the shift in perceptive channels of the light pattern from M-system dominated to P-system dominated or vice versa. The subjective visual effect noticed by an observer depends on the specific design of the light pattern and the parameter that is made to change. Thus for example in the flickered light stimulus described above, a subjective visual effect consists of the sudden appearance of colored patches. Another subjective visual effect associated with the flickered light and perceived at a slightly different flicker frequency is the appearance of a grid or fine geometric pattern, which for some observers is a regular square grid and for others a honeycomb pattern. Yet another subjective visual effect associated with the flickered light is the cessation of the radial movement of subtle shadows, which shadows appear to move away from the center of the illuminated field at lower flicker frequencies, and in the opposite direction at higher flicker frequencies. These three visual effects, the color patches, the grid pattern, and the stopping of the radial movement of subtle shadows, occur at slightly different flicker frequencies in the 20 - 25 Hz range. More than one subjective visual effect is associated with the flickered light stimulus presumably because the M-P crossover for each light stimulus attribute -- color, fine detail, movement -- occurs at slightly different flicker frequency values. A different type of light pattern is described in the section Example 2, a pattern consisting of an apparently-rotating windmill pattern. This type of light pattern has a very clear subjective visual effect associated with the M-P crossove point, which effect consists of a reversal in the direction of apparent rotation of the windmill pattern. The relative sensitivity of the M-system and P-system to a hypothetical variable parameter (e.g., changing frequency of the light flicker) is shown in Figure 1. As indicated in Figure 1 the sensitivity or relative response of the P-system is high when the variable parameter has a low value, which is indicated in Figure 1 as being on the left extreme of the horizontal scale. As the variable parameter increases the relative response or sensitivity of the P- syste decreases. However, the opposite occurs with the M-system. Specifically, the relative response or sensitivity of the M-system is low when the variable parameter has a low value. The sensitivity or relative response of the M-system increases as the value of the variable parameter increases. The point at which the M- and P- systems are stimulated equally is referred to as the crossover point . ro ro ro Hand-held Device A hand-held embodiment of a device 1 shown in the Figure 14 includes a body member 2, a light pattern display 3, patient input switches 4 and 5, alphanumeric display 6 and On/Off switch 7. Other controls or input means (not shown) can provide a means for additional input from the patient, such as information regarding meals, exercise or the amount of insulin taken by the patient. The body member 1 is preferably small enough to fit in the patient's hand 8, pocket or purse The On/Off switch 7 turns the instrument 1 on and off. The light pattern display 3 shows the changing light pattern, for example an apparently rotating windmill wheel 9 This light pattern could be generated, for example by a combination of LEDs, diffusers, filters and lenses, by a solid state screen, by a CRT, or by any other suitable means via signals sent to the screen from a programmable microprocessor. The light pattern includes a fixation pattern 10 in its center, which the patient gazes at during a measurement, and which is used to direct the line of sight and thus control and maintain the position of the light pattern on the retina The patient input switches 4 and 3 allow entering information about the direction of apparent rotation perceived by the patient. The alphanumeric display 6 provides information to the patient e.g , instructions and prompts during the measurement process, information regarding the quality of the measurement, the calculated blood glucose concentration, and previous measurements recalled from the memory The characters 11 in the alphanumeric display 6 should be preferably of large enough size to be readable even by patients with reduced visual acuity To use the device 1, the patient turns on the instrument, looks at the fixation cross 10 in the center of the light pattern 9 and determines the initial direction of apparent rotation of the wheel The patient then presses the input button 4 or 5 that corresponds to the direction perceived and continues to observe the pattern When a reversal n the direction of apparent rotation is perceived, the patient presses the button 4 or 5 corresponding to the new direction of rotation and continues observing the pat ern The patient continues this process of pressing a button 4 or 5 each time the apparent rotation reverses direction, until the instrument determines (via the programmable microprocessor) that enough consistent data has been entered to compute blood glucose concentration with sufficient accuracy The instrument uses the values of the light stimulus parameters at the times when reversals were observed to compute corresponding glucose levels, using previously entered conversion data entered during calibration as described above. The instrument then stops displaying the light pattern 9 and displays the computed blood glucose concentration in the alphanumeric display 6. If the instrument determines that it cannot compute a reliable answer, it will display one of the messages "High", "Low", or "Unable to Measure". Figure 15 is a schematic block diagram showing the principal functional sections of an embodiment including an On/Off switch 7, patient input switches 4 and 5, light pattern display 3, alphanumeric display 6, power supply 12, microprocessor 13 and associated program, memory 14, light pattern control circuit 15 and light output monitor circuit 16. The On/Off switch 7 controls the power to the various components and starts/stops a measuring sequence. Turning on the instrument also initiates a self-diagnostic sequence that includes testing the light sources and other critical components and functions. The light output monitor circuit 16 ensures that the light sources are functional and that their light output is within design levels. This circuit is active from the moment the instrument is turned on and throughout the measurement. The microprocessor 13 is programmed to abort the measurement and to display an informative legend in the alphanumeric display 6 if the circuit detects any fault in the light sources. This protects the user from obtaining erroneous results in the case of a failure in the operation of the light sources. The light pattern control circuit 15 generates the sequence of the light patterns according to the specifications dictated by the microprocessor 13 and associated program. The patient input switches 4 and 5 provide information to the microprocessor 13 as to the timing and direction of the subjective change noticed in the light pattern, e.g., the direction of apparent rotation. Each time an input switch 4 or 5 is pressed, the microprocessor 13 first checks that the correct switch has been pressed, and then reads the value of the variable light stimulus parameter existing at the moment when the switch was pressed. This parameter value information is used by the microprocessor 13 to plan the future changes in the light pattern, and to compute glucose levels, after checking for consistency of the entered data. The microprocessor 13 executes the program, receives input from the patient input switches 4 and 5 and from the light output monitor circuit 16, reads information from, and stores information in memory 14, writes messages on the alphanumeric display 6, and provides information to the light pattern control circuit 15 about display the message "Unable to Measure" . If the correct switch was pressed, the program determines if this was the first time that the switch was pressed. If this is the case, the parameter is allowed to continue changing until the patient detects a reversal. If the switch was pressed for a second time, this means that the patient has detected the first reversal, in which case the program reads and stores the value of the changing parameter at the moment of the switch press. Compensation for the patient's reaction time is described with reference to Figure 17. A time delay (reaction time) exists between the moment when the patient notes a reversal in the direction of rotation and the time when the patient presses the switch. Because of this delay, the parameter value read and recorded by the instrument when the switch was pressed (X 0 + X r ) is slightly higher than the value at the point of reversal (X 0 ) (see Figure 17) . In order to remove this inaccuracy from the reading, a second point of reversal is measured, this time with the parameter changing in the opposite direction. In this example, after the patient pressed the switch to indicate the first reversal and the instrument recorded the parameter value X 0 + X r , the parameter is made to increase by the amount ΔX above X 0 + X r , and then it is made to decrease at the same rate until the patient notices a second reversal. When the patient presses the switch to indicate this second reversal, the program reads the current value of the parameter, which is now X 0 - X r . When the program later averages the recorded values (X 0 + X r ) and (X 0 - X r ) , the error caused by the reaction time, X r , will cancel out and the true value of the parameter at reversal, X 0 , will be extracted. A smaller error will still remain owing to the fact that the number X r is not always the same, but has some statistical variation around a mean value. However, repeated pairs of measurements tend to cancel out this smaller error as well. Thus the feature of reversing the direction of parameter change several times during a measurement, cancels out the effect that the patient's reaction time could have on the measurements. As indicated in the schematic flow diagram of Figure 16, the program takes an even number (n) of such readings of parameter value at reversal, and then proceeds to make a consistency check of those n numbers before proceeding to calculate their average The consistency check examines the differences between pairs of consecutive readings and determines their relative closeness. These readings should be close to each other within a factor that allows for the statistical variation of the patient's reaction time. If all the n-l differences do not meet this criterion of closeness, the instrument cancels the reading and proceeds to display the message "Unable to Measure" . This mechanism provides a safety check that prevents the possibility that either patient errors or the patient's attempts to influence the results could create erroneous readings. Once the readings have passed the consistency check, their average is calculated. The resulting average should be close to X 0 , the parameter value at the point of light pattern reversal, since the effect of reaction time has been removed from the measurement. This average is used to calculate corresponding glucose levels using a look up table stored m memory The table may contain all possible pairs of appropriately rounded-off parameter values and corresponding glucose levels. Alternatively, the table may contain fewer pairs and an interpolation formula may be used to calculate intermediate values . The closest glucose level that corresponds to the averaged value of X is calculated, with an accuracy consistent with the rated accuracy of the device, for example in incremental glucose concentration units of 1 mg/dL The pairs of parameter-glucose values will have been stored in memory at the factory, if it is determined during clinical testing that the same correspondence between parameter values and glucose levels apply to all patients. Alternatively, the numbers will be generated through a calibration procedure if it s determined that each patient requires a different correspondence between parameter values and glucose levels. Subsequent to calculating the glucose level, the program displays the corresponding glucose value if it is within the design limits of the device, otherwise, the program displays the message "High" or "Low", depending on whether the calculated glucose value is above or below the device's design limits The device is preferably designed to read glucose concentrations over the widest possible range, e.g , a range of 10 to 500 mg/dL with the smallest possible error, e.g., ± 1%. However, a useful workable device could be designed to read over a smaller range, e.g , 40-200 mg/dL with a larger acceptable error, e.g , ± 20% Readings can be displayed m standard units used for glucose concentration, such as milligrams per deciliter (mg/dL) , or millimoles per liter (mmol/L) Lastly, the program stores the calculated glucose level in memory, along with the time and date of the measurement, for later analysis or retrieval The program then continues to show the answer for a reasonable length of time, for example 2 minutes, and then turns itself off to preserve battery life This example assumed for s± t licity that a single parameter in the light stimulus changed gradually In practice, more than one parameter can change simultaneously Multi-parameter change can provide less predictable light pattern presentations, a feature that helps avoid measurement errors caused by a patient's inconsistent responses. Multi-parameter change can also provide greater control over the range of measurement. EXAMPLES The following examples are put forth so as to provide those of ordinary skill in the art with a complete disclosure and description of how to carry out the methodology and make and use a device of the invention and are not intended to limit the scope of what is regarded as the invention. Efforts have been made to ensure accuracy with respect to numbers used (e.g., luminance levels, glucose levels, times, etc.) but some experimental errors and deviations should be accounted for. Example 1 A test device as shown in Figure 4 was used to create a series of light pulses having a variable frequency as shown in the graph of Figure 5. The frequency of the light pulses was set to change over time as shown within Figure 5. Specifically, the series of light pulses increased in frequency linearly from 17 Hz to 40 Hz over 9 seconds. Thereafter, the pattern of light pulses decreased in frequency from 40 Hz to 17 Hz in 1 second. The light source was a flash lamp controlled by a signal generator. Each light pulse had an exponential time course with a time constant of 5 milliseconds. The pulses illuminated a diffuser which produced a peak luminance of 800 cd/m 2 . The illuminated area was in the form of a white reflective surface bordered by a black mask. The reflective surface was positioned relative to the patient's field of view so that the surface took up 20° of visual field. Light reflected off of the white reflective surface could enter the eye of the user only via a red Wratten filter which allows the transmission of wavelengths of above 610 nanometers. The subject viewed the field monocularly and fixated the line of sight at the center of the illuminated field. The light pattern consisting of a flickering light caused a perceived characteristic in the pattern consisting of a subtle impression of radial movement. The direction of this radial movement varies with the frequency of flicker. The apparent movement is caused b, a combination of two effects. First, the M-system transmits signals faster than the P-system. Second, while the P- system is most sensitive at the center of the retina the M-system becomes more sensitive towards the periphery. The result is that lower frequencies, which stimulate preferentially the P-system, create an impression of movement away from the center of the retina. However, higher frequencies, which stimulate the M-system preferentially, create an impression of movement towards the center. In short low frequencies cause apparent movement from the center towards the periphery and high frequency flicker creates a perception of movement from the periphery towards the center. An intermediate frequency in the range of 20 Hz to 25 Hz causes the apparent movement to stop for an instant before starting to move in the opposite direction. Three subjects with normal glucose metabolism and vision were tested with the device. Two of the three subjects did not know the purpose of the experiment, or what was changing or being measured in the light stimulus. All subjects were required to press the switch when they noticed that the radial movement stopped before reversing direction. A computer was programmed to read the instantaneous flicker frequency when the subject pressed the switch. The inverse of the flicker frequency, the flicker period, was stored in memory for later analysis. Each measurement took 10 seconds to complete. The average of ten such measurement was recorded automatically as the "critical flicker period" measurement. The subjects had no knowledge of the measurement values during the experimen . In each experiment, the subject's blood glucose level was manipulated with a glucose load in the form of a normal meal following at least 6 hours of fasting Critical flicker period measurements were made at regular intervals -- every 10 to 30 minutes -- starting before the meal and continuing for at least 1 hour and at most 2.5 hours after the meal In close time proximity with these measurements, blood glucose was measured with a conventional home-use invasive blood glucose monitor, specifically a LifeScan One Touch II™ Glucose Meter. The results obtained with different subjects are shown within Figures 6, 7, 8, 9 and 10 wherein each of these figures corresponds to one experiment carried out on one subject. Each graph shows two plots, the upper plot shows the time course of the blood glucose measurements in the subject, while the lower plot shows the time course of the critical flicker period measurements for the same subject, except in Figure 10, that corresponds to an experiment in which blood glucose was not measured. The plots shown within all of the Figures 6 - 10 show that glucose measurements and critical flicker period measurements follow ' the vanes in frame 1 are colored RI, G2, RI, G2, etc., whereas as shown in Figure 12 the vanes in frame 2 are colored R2, Gl, R2, Gl, etc . An image such as that shown in Figure 11 is presented on a screen. That image disappears and is quickly replaced with an image such as that shown in Figure 12. As with the images of a motion picture one image disappears and is quickly replaced by another. By careful choice of the 4 colors RI, G2, R2 and Gl, it is possible to create an impression of continuous rotation. Although only 2 frames are shown in Figures 11 and 12, a total of 4 frames are required to create the impression of smooth and continuous rotation: frame 3 looks similar to frame 1 but has the vane colors switched relative to the colors of frame 1 (G2 vanes should be RI and vice versa) , and frame 4 looks as frame 2 but has the vane colors switched relative to the colors of frame 1 (R2 vanes should be Gl and vice versa) . In practice the sequence of 4 frames is presented repeatedly as a continuous loop, or a "movie", at a rate of, for example, 1 frame per second or up to 40 frames per second, so that the impression of continuous rotation continues for the desired length of time, for example 10 to 30 seconds. The continuous rotation can be clockwise or counterclockwise, depending on the choice of vane colors. For example, if R2 is similar to RI, and Gl is similar to G2, the windmill appears to rotate counterclockwise. On the other hand, the windmill appears to rotate clockwise if Gl is similar to RI and R2 is similar to G2. It is possible to change one or several parameters of the windmill pattern, for example the color or luminance of the vanes, or the color or the luminance of the background, as the sequence of frames is being presented. The windmill images are specifically designed and are changed in a particular manner so as to stimulate the M- and P-systems in sequence while creating a profound visual effect at the M-P crossover point. Specifically, the windmill appears to reverse direction at the M-P crossover point. The image can be created and controlled by a personal computer with the image being generated on a computer monitor. However, the image can be shown on a much smaller screen and generated by a small dedicated programmable microprocessor unit contained within a hand-held device which also includes the screen where the image is shown. Although the operability of the device and method of the present invention does not depend on the exact mechanism responsible for the apparent rotation of the windmill pattern, the following explanation is provided so that those skilled in the art can understand the physiological mechanism that produces the apparent rotation effect and its reversal. When the image is in the form of a windmill as per Figures 11 and 12 and the frame changes from Figure relative stimulation of the M- and P-systems. Depending on which system receives greater stimulation the viewer will perceive rotation m the counterclockwise or clockwise direction. The direction of rotation will continue as long as the original dominant system continues to dominate. However, when the parameters are changed so that the other system dominates the direction of rotation will appear to reverse itself . The point at which the direction of rotation appears to reverse itself is the M-P crossover point. When the viewer notices this point the device is actuated in order to make note of the parameters being projected at this point i.e., the color and luminance of the various components of the windmill. As indicated above in Example 1 the blood glucose level of the individual being tested is then determined by a conventional means. The process is repeated numerous times at various glucose levels over a range in order to calibrate the device. After calibration has taken place the viewer can determine his own glucose level by merely viewing the sequence of apparently rotating windmill patterns and noting the point at which the direction of rotation reverses itself. A windmill pattern similar to the one described above and shown in Figures 11 and 12 was tested using a computer screen and projecting sequential frames or a "movie" of windmill images onto the computer screen at a rate of 1 frame every 0.5 seconds. The windmill outer diameter was 18 mm and was viewed at 508 mm distance, which produced a retinal image 2.25 degrees in diameter. The colors of the windmill vanes were as follows: the RI and R2 vanes were identical, and consisted of a pure red phosphor emission of the CRT screen, with CIE coordinates x=0.63, y=0.34 and luminance 44 cd/m 2 . The Gl and G2 vanes wsre also identical to each other, consisted of pure green phosphor emission with CIE coordinates x=0.28, y=0.60, and were set to a luminance level of 44 cd/m 2 . The background consisted of a rectangular area 25 mm in diameter, surrounding the windmill and filling the clear spaces in each windmill image. The background color was white, and consisted of a balanced mixture of red, green and blue phosphors, and had CIE coordinates x=0.28, y=0.30. The luminance of the background was set to decrease gradually, from 42 cd/m 2 to 30 cd/m 2 in 40 seconds, in steps of 0.3 cd/m 2 at a rate of one step every second. Thus, in this example the variable parameter was the background luminance. This slow rate of change of the variable parameter prevented any effect of the subject's reaction time (time delay between noticing the rotation reversal and pressing the key) on the measurement. This is because reaction times, which have been measured in separate experiments as being from 0.3 to 0 5 seconds long, are shorter than the t me it takes for the variable parameter to change one step (1 second) . The above-specified parameters for the windmill and the background were such that when the movie started playing at the high background luminance, the sequence of windmill images caused a clear impression of counterclockwise rotation. This impression of rotation continued up to a point, when as a result of the background luminance level decreasing gradually, the rotation suddenly appeared to reverse to a clockwise direction. The gradual drop in the background luminance level occurs at such a slow rate that the subject is not aware of a change in the appearance of the windmill or of the background; the subject is only aware of a clear rotation, which is counterclockwise at the beginning, and at some point reverses suddenly and becomes clockwise rotation, and then continued to be clockwise rotation until the end of the movie, when the background luminance level reached its minimum value of 30 cd/m 2 . The subject observed the apparently-rotating windmill pattern from the beginning of the movie, when the background luminance was 42 cd/m 2 , and as the movie progressed and the background luminance decreased gradually the subject continued to observe the pattern until the point when the subject noticed a reversal in the direction of apparent rotation of the windmill, from counterclockwise to clockwise, at which point the subject pressed a key on the computer keyboard. The computer then stopped the movie and displayed the value of the background luminance at the moment when the subject pressed the key, or "critical background level". The entire process took between 10 and 40 seconds. The subject was given a glucose load consisting of a normal meal following at least 6 hours of fasting. Measurements of the critical background level were made approximately every 6 to 10 minutes in the manner explained above The measurements started 0.5 hours before the meal and continued for 1.5 hours after the meal The results obtained are shown m Figure 13. Blood glucose levels were not measured in this experiment by conventional means. However, results obtained show that the critical background levels changed with time and that the time course of these changes followed the expected changes in the subject's blood glucose levels. These results demonstrate that for a light pattern consisting of the windmill pattern with variable background described above, the critical parameter level, or value of the variable parameter when the observer noticed the subjective visual effect -- in this case the reversal in the direction of apparent rotation -- changed in parallel with changes in blood glucose Per the explanation advanced earlier regarding the mechanism that produces apparent rotation and its direction reversal, the results of this experiment are consistent with the assumptions that the sub j ective visual effect is associated with the M-P crossover point, and that the M-P crossover point shifts in parallel with changes in glucose level. The instant invention is shown and described herein in what is considered to be the most practical, and preferred embodiments. It is recognized, however, that departures may be made therefrom which are within the scope of the invention, and that obvious modifications will occur to one skilled in the art upon reading this disclosure.

Claims: CLAIMS What is claimed: 1. A method for measuring the blood glucose concentration of a subject, said method comprising: a) providing a light pattern which provides a greater amount of stimulation to a first retinal system relative to a second retinal system, resulting in a first:second stimulation ratio greater than one, wherein said light pattern stimulates a subjective visual characteristic which varies with the first:second stimulation ratio, and wherein the sensitivity of said first retinal system and said second retinal system to said light pattern changes with the blood glucose concentration of said sub ect; b) allowing said subject to observe said subjective visual characteristic of said light pattern; and c) correlating said subjective visual characteristic with said subject's blood glucose concentration. 2. The method of claim 1, wherein a parameter of said light pattern is varied so as to alter the first:second stimulation ratio. 3. The method of claim 2, wherein at least a portion of said light pattern changes over time with respect to a parameter selected from the group consisting of color, luminance level, contrast, shape, size, position, detail content, texture, speed of movement, direction of movement and rate of flicker. 4. The method of claim 1, wherein said first and second retinal systems are selected from the group consisting of the M- retinal system and the P-retinal system, wherein said first and second systems are not identical . 5. A device for measuring the blood glucose level of a subject, said device comprising: a body; and display means contained within said body for generating a light pattern which provides a greater amount of stimulation to a first retinal system relative to a second retinal system, resulting in a first:second stimulation ratio greater than one, wherein said light pattern stimulates a subjective visual characteristic which varies with the first: second stimulation ratio, and wherein the sensitivity of said first retinal system and said second retinal system to said light pattern changes with the blood glucose concentration of said subject; wherein said light pattern is selected so that it will have a first subjective visual appearance when the subject's blood glucose level is below a predetermined concentration, and will have a distinctly different appearance when the subject's blood glucose level is above said predetermined concentration. 6. The device of claim 5, wherein said display means comprises means for varying a parameter of said light pattern such that the first:second stimulation ratio is decreased. 7. The device of claim 6, further comprising: actuation means, which is actuated to indicate observation of a subjective visual effect; processor means, which is capable of measuring said parameter when actuated, and correlating said measured parameter with a corresponding blood glucose level; and means for displaying information about blood glucose levels. 8. The device of claim 7, wherein said light pattern is selected from the group consisting of flickering light and rotating windmill images, and said subjective visual appearance is selected from the group consisting of appearance of colors, disappearance of colors, appearance of a regular geometric pattern, disappearance of a regular geometric pattern, appearance of radial movement, disappearance of radial movement, and reversal in direction of rotation. 9. The device of claim 5, wherein said processor includes information on a range of parameter values associated with the presence of a subjective visual effect, along with the corresponding blood glucose levels for said subject. 10. The device of claim 5, wherein said processor is programmed to avoid erroneous measurements by making redundant measurements, checking the consistency of the subject's responses, and canceling any effect created by the subject's reaction time.

Inventors: CASTANO JAIME A, CASTANO, JAIME, A.
Applicants: CASTANO JAIME A, CASTANO, JAIME, A.
Application year: 1997
Main classification: A61B13
IPC codes: A61B5, A61B13, A61B19