APPARATUS AND METHOD FOR INFECTIOUS DISEASE DETECTION

Abstract: A process for detecting HIV infection, Hepatitis A, B and C, and other similar infections in a plasma sample, wherein the process involves the use of an excitation laser source to irradiate upon the plasma sample an excitation laser beam to obtain a fluorescence emission spectrum of the plasma sample. The invention uses an excitation laser wavelength of about 355 nanometers. Detection of the fluorescence is made in the wavelength range from about 380 to 600 nanometers. The resulting spectrum of the sample is compared with the spectrum of a control which is free from infection. Analysis of the parameters of the emission spectra including, but not limited to, peak intensity wavelength, amplitude at the peak intensity, area ratio of left and right portions of the emission spectra, and shifts of the peak intensity wavelength, allows determination of HIV infection, Hepatitis A, B and C, and other similar infection in the plasma. Selective absorbents, such as C-M Affi Gel Blue and activated charcoal, may be used to treat the samples before fluorescence measurements, which his found to improve discrimination of infected and uninfected samples. The present invention is capable of detecting HIV infection at the stage when it is still undetectable by conventional diagnosis methods.

Description: APPARATUS AND METHOD FOR INFECTIOUS DISEASE DETECTION Field Of The Invention The present invention relates to the detection of the presence of infectious disease and more particularly to detection of the presence of HTV infection, Hepatitis A, B and C 10 infection, and other similar infections by optical means. Background Of The Invention Optical systems have been used to determine chemical compositions of matters. Such optical systems include lasers which have long provided impetus to a wide range of spectroscopic investigations. The many advantages of lasers, such as their monochromaticity (ability to operate within a very narrow wavelength range), very high intensity compared to diffuse light sources, such as mercury lamps, and availability of inexpensive laser sources, are allowing many types of experiments and measurements not 20 previously possible. Nowadays, the use of lasers in experiments or tests, such as absorbance or fluorescence measurements in chemical analysis, is routine. Experiments or measurements based on the absorption or emission of light upon illumination of a sample by a light source have long been used to determine the nature of a . sample's various components. The principle is based on the fact that given a high enough resolution for the measuring spectroscopic apparatus, every chemical component will give rise to a different absorption or emission (referred to hereinafter as fluorescence) spectrum which is a plot of the intensity of light absorbed or emitted by a sample measured at various wavelengths of the incident or emitted light. The absorption or fluorescence spectrum 30 therefore corresponds to a fingerprint of a given chemical component, allowing its discrimination from other components present in the same sample. Absorption or fluorescence spectroscopy has been an important technique for identification of unknown biological substances in aqueous (water-based) solutions. An 35 absorption or fluorescence spectrum, of an aqueous solution, however, may be complicated 1 - by the fact that absorption bands of the various biological substances in the solution sometimes overlap, particularly in the case of large molecules, such as biomolecules, making assignments of their origins difficult. There is, in addition to absorption or fluorescence signals originating from a component of interest, a large amount of background noise generated by water and other constituents present in biological samples, such as blood or plasma. Currently, a number of simple-to-operate, non-optical based analyzers for detection of certain infectious diseases, such as HTV infection, are commercially available. Examples ofsuch analyzers are Ektachem DT 60, Ektachem 700P, Reflotron, and Seralyzer. These systems allow tests to be performed in settings outside traditional laboratories, e.g., outpatient clinics, physicians' offices, and even shopping malls, schools, or churches. In addition, these systems offer the advantage of being economical, compact, lightweight, easy-to-operate, convenient, and requiring only a small amount of test sample. Some of these analyzers also have the potential for providing test accuracy precision similar to those obtained from more sophisticated analyzers used in large clinical laboratories. However, none of these commercially available analyzers are understood to be optical-based. Moreover, these systems are not suitable for analysis of a large number of samples. In addition, no such simple-to-operate system exists for detecting Hepatitis A, B or C infection. Another drawback of available analyzers for detecting HTV infection is that they are not sufficiently sensitive and thus incapable of detecting HTV infection at the early stage of the infection. Only when the infection has occurred for some time such that the antibody or antigens of the HTV viruses in the blood sample reach detectable level, can the HTV infection be detected by conventional analyzers. US Patent 5, 267, 152 to Yang et al. discloses an optical technique for a non- invasive measurement of blood glucose concentration using a near-infrared photodiode laser. Yang et al. determines the blood glucose concentration using an algorithm based upon the characteristic translational, vibrational and rotational motions of the molecules in the blood resulting from the excitation of the sample with a diode laser, and then comparing the optical signal from light reflected off the blood constituents with a calibration curve previously stored in the memory of a microprocessor. However, Yang et al. does not - 2 - measure changes in the emission spectra of biological samples as a result of changes in the amounts of certain metabolites in the samples. US Patent 5,258,788 to Furuya discloses an optical method for measuring the protein composition and concentration of the aqueous humor of the eye which, in addition to proteins, also contains blood cells. However, Furuya does not measure the emission of light by the constituents of a sample as a result of irradiation of the sample with a laser beam. Instead, it measures the scattering of incident light off the sample molecules rather than on the emission of light by the molecules themselves as a result of irradiation with a laser beam. US Patents 5, 238, 810 and U.S. 5, 252, 493 both to Fuβwara et al. disclose an optical-based immunoassay method in which antigens or antibodies are labeled with micro- particles of a magnetic substance to form a magnetic labeled body, thus allowing determination of minute amounts of the antigen or antibody. It would be desirable if viruses be optically detected without the use of magnetic particles. It is therefore an object of the present invention to provide identification of a wavelength range of an excitation laser beam within which the fluorescence spectrum of the sample will provide information that can be used to detect and identify any infectious disease present in the sample. Also the present invention provides for identification of a fluorescence wavelength range within which the fluorescence spectrum of a sample will yield information that may be used to detect and identify any infectious organism contained in the sample. Also various parameters obtained from the fluorescent spectrum of a sample may be used to detect and identify any infectious disease contained in the sample. Thus the present invention provides apparatus and method for detecting HTV infection at an earlier stage when they are yet to be detectable by conventional methods. Summary Of The Invention . , The present invention is directed to detection of presence of an infection in a plasma, which comprises the steps of (a) obtaining the plasma; (b) preparing a sample from the plasma; (c) directing laser light of a predetermined wavelength onto the sample; (d) obtaining an emission spectrum from the sample; and (e) comparing the emission spectrum with a control spectrum to determine presence of the infection in the sample. Preferably, - 3 the laser light has a wavelength between about 270 and 400 nanometers and more preferably, between about 310 and 370 nanometers. In a preferred embodiment, a pulsed laser excitation at a selected wavelength is irradiated onto a plasma sample, and the resultant fluorescence spectra between a particular wavelength range of interest is detected and analyzed. The present invention allows for the differentiation between normal human plasma (uninfected) and plasma from individuals infected with human immunodeficiency viruses (HTV), Hepatitis A, B and C, and other similar infectious diseases. In accordance with the preferred embodiment of the present invention, an excitation laser wavelength of about 355 nanometers (nm) is selected to generate fluorescence from a human plasma that will yields useful information for infectious disease detection and identification. In addition, a fluorescence wavelength range of about 380nm to 600nm is selected for fluorescence detection, because within this wavelength range, the fluorescence spectrum of the samples is found to provide useful information for infectious disease detection and identification. In the preferred embodiment, excitation of human plasma is at approximately 355nm, which elicits an emission spectrum attributed to a set of relatively lipophilic molecules associated with the metabolic status of the individual, such relatively lipophilic molecules being in large part bound to albumin and to low and very low density lipoproteins ("LDL"). Several parameters of these spectra have been identified which clearly differentiate HTV positive plasma from HTV negative plasma, or plasma infected with Hepatitis A, B or C from normal uninfected plasma. These parameters includes, but not limited to, the wavelength at which the peak emission intensity is obtained; the amplitude of the peak emission; and the area ratio of the left and right portions of the emission spectra (defined in detailed below). In addition, HTV positive and negative plasmas may be distinguished by using an algorithm having one or more of these parameters as variables. In the present invention, plasma samples may be first treated with selective absorbents, such as C-M Affi Gel Blue or activated charcoal, to improve the discrimination of these parameters for infected and uninfected samples. For example, it is found that C-M Affi Gel Blue significantly shifts the peak wavelength of an emission toward a lower 4 - wavelength. Advantageously, this peak wavelength shift is significantly greater for HIV positive samples than for HIV negative (normal) samples, thus allowing improved discrimination of the HTV positive and negative samples on the basis of the peak wavelengths of the samples. In addition, for samples treated with C-M Affi Gel Blue, it is also found that the intensity of the fluorescence peak is reduced more in HIV negative samples than in HIV positive samples,. This improves the ώscrimination of the HTV positive samples from HIV negative samples on the basis of intensity or amplitude of the emission peak. Further, it is found that HTV positive samples treated with activated charcoals exhibit a smaller shift of the emission band than in HTV negative samples treated with activated charcoal, which enhances the discrimination of the infected and uninfected samples on the basis of peak wavelengths. The present invention provides a more sensitive detection of HIV infection particularly at the early stage of the infection than conventional diagnosis methods. For example, in instances where samples from an individual infected with HTV viruses at the early stage when the infection is still undetectable by conventional diagnosis, it is detected by using the method and apparatus of the present invention. Brief Description Of The Drawings These and other features, objects, and advantages of the present invention will become more apparent from the following detailed description in conjunction with the appended drawings in which: Figure 1 is a schematic block diagram of an infectious disease detection system of the present invention; Figure 2 is a schematic circuit diagram of a detector/exposure control portion of the d Λi-sease d ,etection system; Figure 3 shows fluorescence spectrums of an HIV negative plasma sample and HIV positive plasma sample produced at an excitation wavelength of 355 nm and detected within the wavelength range of 350 nm to 600 nm; Figure 3 A shows fluorescence spectrums of a group of HTV positive plasma samples and a group pf HTV negative plasma samples; Figure 4 illustrates the fluorescence spectrums of HTV negative and positive samples as well as such samples treated with DEAE-Affi Gel Blue; Figure 5 illustrates the fluorescence spectrums of peptide, HTV positive and negative samples; Figure 6A illustrates the fluorescence spectrums of holo-albumin (HSA) and fatty acid free albumin; Figure 6B illustrates the fluorescence spectrum of LDL; Figure 7 illustrates the fluorescence spectrums of HTV positive and negative samples as well as such samples treated with TCA; Figure 8 illustrates the fluorescence spectrums of HTV positive and negative samples as well as such samples acidified and dialyzed; Figure 9 A illustrates the fluorescence spectrums of a group of HTV positive and HTV negative samples and an HSA sample; Figure 9B illustrates the fluorescence spectrum of LDL; Figure 10 illustrates the fluorescence spectrums of HTV positive and HTV negative 0" samples, respectively, and such samples treated with CM- Affi Gel Blue (CM-AGB); Figure 11 illustrates the fluorescence spectrums of HTV positive and HTV negative samples, an NADH sample and a sample of a mixture of NADH and HSA; Figure 12 illustrates the fluorescence spectrums of an NADH sample and such 5 sample treated with activated charcoal; Figure 13 illustrates the fluorescence spectrums of thiocrome, a mixture of thiocrome, NADH and HSA, and HTV positive and negative samples; Figures 14A-D illustrate the fluorescence spectrums of NADH, thiocrome, riboflamin, and HDL; 0 Figure 15 illustrates the fluorescence spectrum of an HTV negative sample and a reconstructed spectrum; Figure 16 illustrates the fluorescence spectrum of an HTV positive sample and a reconstructed spectrum; 5 6 - Figure 16A illustrates the fluorescence spectrums of a group of HIV positive samples and a group of HIV negative samples; Figure 16B illustrates the fluorescence spectrums of the HIV positive and HIV negative samples of Figure 16 A but normalized at 550 nm; Figure 16C illustrates the fluorescence spectrums of the HIV positive and HIV negative samples of Figure 16A treated with CM-AGB; Figure 16D illustrates the fluorescence spectrums of the CM-AGB treated HTV positive and HTV negative samples of Figure 16C but normalized at 550 nm; Figure 17 A illustrates the fluorescence spectrums of another group of HTV positive samples and another group of HTV negative samples; Figure 17B illustrates the fluorescence spectrums of the HTV positive and HTV negative samples of Figure 17A but normalized at 550 nm; Figure 17C illustrates the fluorescence spectrums of the HTV positive and HTV negative samples of Figure 17A treated with CM-AGB; Figure 17D is the fluorescence spectrums of the CM-AGB treated HTV positive and CM-AGB treated HTV negative samples of Figure 17C but normalized at 550 nm; Figure 18 illustrates the fluorescence spectrums of an HTV positive plasma and an HTV negative plasma samples for demonstratmg the definition of an "area ratio" parameter; Figure 19 shows emission peak amplitudes of a group of HIV positive and negative samples normalized at 550 nm with and without CM-AGB treatement; Figure 20 shows the emission peak wavelengths of the same HTV positive and negative samples of Figure 19 with and without CM-AGB treatment; Figure 21 shows the area ratios of the same HTV positive and negative samples of Figure 19 with and without CM-AGB treatment; Figure 22 shows amplitude changes of the same HTV positive and negative samples of Figure 19 after the CM-AGB treatment; Figure 23 shows wavelength changes of the same HIV positive and negative samples of Figure 19 after the CM-AGB treatment; Figure 24 shows area ratio changes of the HTV positive and negative samples after the CM-AGB treatment; Figure 25 illustrates a process flow chart according to the present invention; - 7 Figures 26A-C show early detection of HIV infection of untreated samples as compared with control samples; Figures 27A-C show early detection of HTV infection using the same samples of Figures 26A-C after CM-AGB treatment as compared with control samples; Figure 28 illustrates a table setting forth time and test results of the same samples of Figure 26A-C tested by conventional methods; Figure 29 shows the emission peak amplitude differences of Hepatitis infected samples between the samples treated with CM-AGB and the same samples treated with activated charcoal and their comparison to those of non-Hepatitis infected control samples; Figure 30 shows the area ratio differences of the same Hepatitis infected samples of Figure 29 between the samples treated with CM-AGB and the same samples treated with activated charcoal and their comparison to those of non-Hepatitis infected control samples; Figure 31 shows the peak emission wavelengths of the same Hepatitis infected samples of Figure 29 as compared with those of non-Hepatitis infected control samples; Figure 32 shows peak emission amplitude differences of the same samples of Figure 29 between the samples treated with CM-AGB and the same samples treated with activated charcoal and their comparison to those of non-Hepatitis infected control samples; Figure 33 shows peak emission wavelength differences of the same samples of Figure 29 between the samples treated with CM-AGB and the same samples treated with activated charcoal and their comparisons to that of non-Hepatitis infected control samples; Figure 34 shows a comparison of the parameters of peak emission amplitude of samples treated with CM-AGB divided by peak emission wavelength of the same sample but treated with activated charcoal between certain Hepatitis infected samples and non- Hepatitis infected control samples; Figure 35 shows a comparison of the parameters of of certain samples for Hepatitis detection; Figure 36 shows area ratios of certain samples for Hepatitis detection; Figures 37 shows normalized peak amplitude measurement results for Hepatitis detection; Figure 38 shows peak wavelength measurement results for Hepatitis detection; Figure 39 shows area ratio changes of certain treated samples for Hepatitis detection; Figure 40 shows amplitude changes of certain treated samples for Hepatitis detection; Figure 41 shows peak wavelength changes of certain treated samples for Hepatitis detection; Figure 42 shows area ratio changes of certain treated samples for Hepatitis detection; Figure 43 shows amplitude changes of certain treated samples for Hepatitis detection; Figure 44 shows peak wavelength changes of certain treated samples for Hepatitis detection; Figure 45 shows composite parameters of certain samples for Hepatitis detection; and Figure 46 shows different composite parameters of certain samples for Hepatitis detection. - 9 Detailed Description Of The Invention A detection system 10 according to the present invention, in reference to FIG. 1, utilizes the bundling of a laser input (L), biologic phenomena (B) and signal recognition (S), which is referred hereinafter as an LBS system. This system provides for detecting infectious diseases and will be referred herein as an "Infectious Disease LBS". The System 10 uses a pulsed laser to excite human plasma at a selected wavelength and provides an analysis of parameters in the resultant fluorescence spectra about a particular wavelength range of interest. The Infectious Disease LBS of the present invention allows for the differentiation between normal human plasma and plasma from individuals infected with human immunodeficiency viruses (HTV), Hepatitis A, B and C, as well as other similar infectious diseases. In accordance with the present invention, an excitation laser wavelength between about 270 nm and about 400 nm is selected to generate fluorescence from a human plasma that yields useful information that can be used for disease detection and identification. More preferably, the excitation laser wavelength is between about 310 nm and 370 nm. In the preferred embodiment described herein, an excitation laser wavelength of 355 nm is selected. This wavelength (i.e., 355 nm) is selected within the preferred excitation laser wavelength range (i.e., between about 270 nm and 400 nm) mainly because it is easily available from the particular laser source used by applicants; other wavelengths within the preferred wavelength range between about 310 nm and about 370 nm, such as 340 nm or 360 nm, may also be used for infectious disease identification and detection. Thus, in this respect, it should be understood that the present invention is not limited to the excitation laser wavelength of 355 nm as described herein. Applicants found that if the excitation laser wavelength is less than 270 nm or greater than 400 nm, the background fluorescence signal from human plasma that is not believed to significantly contribute to infectious disease detection becomes so great that signals useful for infectious disease detection are not easily distinguishable from this background signal. In addition, according to the present invention, a fluorescence wavelength range of about 380nm to about 600nm is identified by applicants as the fluorescence wavelength range that provides useful information for disease detection and identification. 10 - An important aspect of the present invention is that excitation of human plasma by a laser excitation having a wavelength within the range of about 270 nm to 400 nm, and more preferably within the range of about 310 nm to 37 nm, and such as 355nm, elicits an emission spectrum which is attributed to a set of relatively lipophilic molecules associated 5 with the metabolic status of the individual, such relatively lipophilic molecules being in large part bound to albumin and to low and very low density lipoproteins. As will be detailed below, several parameters of these spectra have been identified which clearly differentiate HTV positive plasmas from HTV negative plasmas; or plasmas infected with 10 Hepatitis A, B or C and normal, uninfected plasmas. According to the present invention, HTV positive and negative plasmas are distinguished by their respective wavelengths ( ^ at which their respective emission intensity profile exhibit maximum emission intensities (or amplitudes), and by the relative values ofsuch the maximum intensities ([„, « ) (or amplitude which is proportional to the square root of intensity). In addition, according to the present invention, additional parameters, beside ^ and I,^ for distinguishing HTV positive plasmas from HTV negative plasmas are also provided. One of such parameters is the so-called area ratio, A,, which will be defined in detail. In accordance with the preset invention, chromatography of the plasma through 2 ^Ω υ certain absorbents differentially alter these parameters in HTV positive plasma and HTV negative plasma samples, allowing a greater identification and distinction of an HTV positive sample. These absorbents include C-M Affi Gel Blue (hereinafter also referred to as "CM-AGB") and activated charcoal. It is found that the emission spectra of a plasma 25 sample, after it is treated with CM-AGB, exhibit a significant shift in wavelength towards lower wavelength. Advantageously, this shift is significantly greater for HTV positive samples (about 12-18nm) than for HTV negative (normal) samples (about 4-8nm). This effect helps to more clearly discriminate the HTV positive samples and HTV negative samples. It is also found that the intensity of the fluorescence peak, !„ « , is reduced more in 30 HTV negative plasma samples than in HTV positive plasma samples by C-M Affi Gel Blue treatment. Applicants also found that activated charcoal treatment of the plasma samples results, advantageously, in a relatively smaller shift (towards shorter wavelengths) of the 35 - 11 emission band for HTV positive samples (about l-2nm) than for HTV negative samples (about 5-8nm). Referring to FIG. 1, in a preferred embodiment, an Infectious Disease LBS system 10 of the present invention includes a frequency-tripled NdYag laser 15 having an emission wavelength of about 355 nm, an average power of about 2 milliwatts, and pulsed at a high repetition rate (e.g., lOHz or 20Hz) by a mechanical shutter 20. When shutter 20 is open, a small portion of the laser beam emitted by laser 15 is reflected into a silicon detector 25 by a beam splitter 30 as input to a beam monitor 35. A schematic circuit diagram of beam 0 monitor 35 is depicted in FIG. 2A. Beam monitor 35 monitors the total amount of light irradiated onto the sample to ensure that each sample under test is irradiated with the same amount of light. More specifically, an diode detector 25 detects the portion of light reflected by mirror 30. A circuit including a pre-amplifier 26 measures the total amount of light irradiated on detector 25 and when it reaches a predetermined level, a comparator 27 triggers a control flip flop to control a shutter solenoid 29 to turn off the shutter. FIG.2B illustrates the waveforms of the shutter and voltages at Pl and P2 of the monitor circuit The remainder of the laser beam, after passing beam splitter 30, goes into a focusing lens 40 which focuses the beam into an optical fiber 45, the output of which is connected to 0 a lens 50. Lens 50 collimates the laser beam before providing it into a quartz cuvette 55 containing a sample to be tested (analyte). A mirror 60 is used to approximately double the effective excitation energy. When the laser beam is irradiated onto the sample contained in cuvette 55, an optical emission is produced by the sample, which passes through a high-pass _ < - optical filter 65 to cut off any scattered light of a wavelength of 355nm (the input laser wavelength) from the laser source, thereby ensuring that the scattered light from the input excitation beam does not interfere with the emission originating from the sample. The sample emission is then collected by another focusing lens 70, which focuses and provide the sample emission into another optical fiber 75. Another reflective mirror 80 is used to 30 effectively approximately double the sample fluorescence collection efficiency. The output of optical fiber 75 is connected to a CCD (charge-coupled device) array spectrometer 85 which collects the fluorescence spectrum of the emission from the sample. The output signal from CCD spectrometer 85 is provided to a personal computer 90 which is used to 35 - 12 - initiate the data collection sequence, collect data from the spectrometer, and perform the analysis as detailed below. In accordance with the present invention, the fluorescence spectrum of human plasma of a person is used to determine if that person is infected with certain infectious diseases, such as HTV, Hepatitis A, B and C, or other similar infectious disease. Human plasma contains as many as 100 to 125 proteins, many of which, such as albumin and the lipoproteins, serve as carriers for smaller metabolically important molecules, as well as their metabolites. Applicants of the present invention discovered that the emission spectrum 1 o between about 380nm and about 600nm can be ascribed to a limited number of these constituents, and these constituents, when present in different relative concentrations, result in a spectrum in which the total fluorescence and emission maximum is shifted to relatively shorter wavelengths for HTV positive plasmas, and to longer wavelengths for HTV negative plasmas. 15 Referring to FIG. 3, which shows the emission spectra of HTV negative (a solid line) and positive (a broken line) whole plasma samples, it is demonstrated that the fluorescence spectrums for the HTV negative plasma and HTV positive plasma exhibit difference peak locations (i.e., wavelength maxima) at which the spectrums exhibit a maximum intensity 20 and different relative intensity (i.e., amplitude). This is further demonstrated by the emission spectrums of HTV positive plasmas (Dl, D3, D6, D8, Dl 1, D13, D15, D16, D19 and D20) and emission spectrums of HTV negative samples (D2, D4, D5, D7, D9, D10, D12, D14, D17 and D18) shown in FIG. 3 A. There is a clear separation between the HTV _ _ positive spectra group and the HTV negative spectra group. In accordance with the present invention, methods are provided to alter both the amplitude and wavelength maxima of the plasma spectrum to further discriminate HTV positive and negative samples. It is believed that these methods alter the relative conceentration of the contributing fluorophores (the constituents that give rise to the 30 observed fluorescence), which results in the shift in the amplitude and wavelength maxima of the samples. These findings are supported by the following experiments or tests conducted by applicants. Referring to FIG. 4, the fluorescence emission of eluates obtained by 35 chromatographic absorption of plasma on DEAE-Affi Gel Blue (BioRad Laboratories) 13 - (which essentially represent purified immunoglobulins) shows that it contains less than 2 percent of the fluorescent signal from whole plasma, indicating that the emission profile of the plasma is not due to immunoglobulins. FIG. 4 shows the emission spectrum of eluates made by chromatographic absorption of an HTV negative sample (designated as 100 - a thick solid line); the emission spectrum of eluates made by chromatographic absorption of an HTV positive sample (designated as 102 - a thick broken line); the emission spectrum of a whole plasma of an HTV negative sample (designated as 104 - a thin solid line); and the emission spectrum of a whole plasma of an HTV positive sample (designated as 106 - a thin broken line). Referring to FIG. 5, applicants found that purified synthetic polypeptides αmtaining 18 of the most commonly occurring amino acids, including phenylalanine, tyrosine, proline and tryptophan, fail to give a significant emission spectra, which indicates that the emission profile of whole plasma in the wavelength range of about 350 nm to about 600nm is not directly due to a protein or polypeptide. FIG. 5 shows the emission spectrum of the purified synthetic polypeptides (designated as 108 - a thick solid line); the emission spectrum of an HTV negative whole plasma sample (designated as 110 - a thin solid line); and the emission spectrum of an HTV positive whole plasma sample (designated as 112 - a broken line). Referring to FIGS. 6A and 6B, analysis of commercially obtained human serum albumin (HSA) (FIG. 6A) and low density lipoprotein ("LDL")(FIG. 6B) shows that each yields an emission profile very similar to that obtained from whole plasma. In FIG. 6A, the emission spectrum designated as 114 (a thick solid line) is obtained from a fatty acid free HSA sample; and the emission spectrum designated as 116 (a thin solid line) is obtained from an HSA sample. Since purified polypeptides yield virtually no emission signal, applicants concluded that the HSA and LDL emission signals result from molecules bound to them, but not due to the protein itself. This is in part confirmed by applicants by taking the fluorescence spectrum of albumin commercially treated with charcoal to remove lipids and other relatively hydrophobic molecules ("essentially fatty acid free albumin")( see emission spectrum designated as 114 of FIG. 6A): the resulting spectrum showed an emission band which has a much reduced intensity relative to that of holo-albumin. From these results, it is concluded that the observed shift in the emission spectra suggests the removal by charcoal of some fluorophores which may contribute to a positive (with HIV 14 - viruses) or negative (no detectable HTV viruses) spectra. Similar tests by applicants with LDL adsorbed by charcoal show a significant decrease in total fluorescence as well as a shift in the spectrum, which suggests that charcoal removes mainly those components bound to LDL that contribute to the emission profile. It is therefore concluded by applicants that charcoal shifts negative HTV plasma, but not HTV positive plasma Referring to FIG. 7, plasma in which proteins were precipitated out using trichloroacetic acid ("TCA") yields a fluorescence spectrum showing a significantly reduced emission intensity relative to that of whole plasma. Applicants thus confirmed that the 1 o source of the emission spectra in the wavelength range of interest may be bound to proteins including albumin and LDL. In FIG. 7, the emission spectrum designated as 118 (a thick solid line) is obtained from an HTV negative plasma sample treated with TCA; the emission spectrum designated as 120 (a thick broken line) is obtained from an HTV positive plasma sample treated with TCA; the emission spectrum designated as 122 (a thin solid line) is obtained from the HTV negative plasma; and the emission spectrum designated as 124 (a thin broken line) is obtained from the HTV positive plasma sample. Referring to FIG. 8, the hydrophobicity of these constituents or the hydrophobic rather than the ionic nature of their binding to a protein was demonstrated by the results of 20 experiments which showed little change in spectra upon changing the charge on plasma proteins with acidification to pH 4.0 and subsequent dialysis using membranes with a molecular weight cutoff of 12 kilodaltons. In FIG. 8, the emission spectrum designated as 126 (a thin solid line) is obtained from an HTV negative plasma sample; the emission _ . spectrum designated as 128 (a thick solid line) is obtained from the same HTV negative plasma sample treated by the above described acidification and dialysis process; the emission spectrum designated as 130 (a thick broken line) is obtained from an HTV positive plasma sample treated by the above described acidification and dialysis process; and the emission spectrum designated as 132 (a thin broken line) is obtained from the same HIV 30 positive plasma sample treated by the above described acidification and dialysis process. Referring to FIGS. 9A and 9B, the spectra of commercially obtained holo-albumin and LDL closely approximate the spectrum of human plasma. This indicates that a large proportion of the constituents which contribute to the overall emission profile are bound to 35 albumin and LDL. 15 - Referring to FIG. 10, it has been discovered by applicants that all formulations of CM- Affi Gel Blue (AGB) columns, if used in a high enough ratio relative to plasma, will remove some or all of the fluorescence emission signal. This suggests that this gel has affinity for at least some or all of the fluorophores present in the sample plasma. Cibacrom gels, which contains the same Cibacrom dyes that in CM-AGB, bind other proteins as well, and one common feature of many these proteins is their ability to bind to NADH. It is believed that NADH may acts as a contributing fluorophores in the plasma samples. In FIG. 10, the emission spectrum 140 (a thick solid line) is obtained from an HTV negative o sample plasma treated with AGB; the emission spectrum 142 (a thick broken line) is obtained from an HTV positive sample plasma treated with AGB; the emission spectrum 144 (a thin solid line) is obtained from the same HTV negative sample plasma without the AGB treatment; the emission spectrum 146 (a thin broken line) is obtained from the same HTV positive sample plasma without the AGB treatment. 15 Referring to FIG. 11, analysis of NADH (reduced nicotinamide adenine dinucleotide) yielded a spectrum which overlaps with the spectrum of whole human plasma derived from a negative plasma, also referred to in this application as a "normal" plasma. Applicants found that the oxidized form, NAD, has no fluorescence in the 380-600 nm 0 wavelength range so that oxidation of a sample resulting in the conversion of NADH to NAD could lead to false positives. Subsequent studies mixing NADH with "essentially fatty acid free" (charcoal treated) albumin gave an emission spectrum which even more closely resembled the negative plasma's emission profile. These results indicate that _ . NADH, possibly in a protein bound form, is an important contributor to the plasma's emission profile. In fact, it has been documented that the presence of HTV viruses results in a reduction in niacin and NADH through the effects of interferon gamma's induction of the catabolism of tryptophan, the obligatory precursor to niacin. In FIG. 11, an emission profile designated as 148 (a thick solid line) is obtained from NADH; an emission profile 30 designated as 150 (a thick broken line) is obtained from a mixture of NADH and HSA; an emission profile designated as 152 (a thin solid line) is obtained from an HIV negative sample plasma; and an emission profile designated as 154 (a thin broken line) is obtained from an HIV positive sample plasma. 35 16 - Referring to FIG. 12, additional studies by applicants have served to reinforce the importance of NADH. Chromatography of plasma through charcoal results in a large reduction in fluorescence while a similar exposure of NADH to charcoal quantitatively removes its signal. In a complex mixture of fluorophores, the relatively selective removal of some fluorophores, such as NADH, results in a shift in the wavelength of maximum absorption of the aggregate emission spectrum. NADH emits on the long wavelength side of the plasma emission maximum. Thus, any treatment that results in the relatively selective removal of NADH is expected to lead to an overall shift of the emission band towards shorter wavelengths. Applicants found this to be true for all plasma treated with activated charcoal. Moreover, applicants found that a charcoal-treated HTV negative plasma exhibits a greater shift of the fluorescence maximum towards shorter wavelengths than a charcoal-treated positive plasma sample, which suggests that NADH or related molecules have a greater contribution to the emission arising from a negative plasma sample than to that arising from a positive. In FIG. 12, an emission profile designated as 156 (a solid thick line) is obtained from a charcoal treated NADH sample; and an emission profile designated as 158 (a thin solid line) is obtained from an NADH sample. Referring to FIG. 13, analysis of the thiamine metabolite, thiochrome, yielded an emission spectrum with a maximum very similar to those of HTV positive samples. FIG. 13 shows the emission profiles obtained, respectively, from thiochrome (designated as 160, a thick solid line), a mixture of thiochrome, NADH and HSA with certain proportions (designated as 162, a thick broken line), an HTV positive plasma sample (designated as 164, a thin broken line), and an HTV negative plasma sample (designated as 166, a thin solid line). It is shown that the mixed sample containing NADH, thiochrome and albumin yielded a spectrum similar to that of a whole plasma sample. These data suggest that these metabolites (NADH, thiochrome, and albumin), in both free and bound forms, make important contributions to the emission spectrum of a human plasma For completeness, the emission profiles of samples of NADH, thiochrome, riboflamin and HDL are shown in FIGS. 14A-D, respectively. In addition, these data allow one to determine dynamic conditions in which an individual's metabolic status can be assessed based on steady state changes in the relative amounts of these metabolites and similar molecules. As an example, alterations in the - 17 - relative contributions of the aforementioned metabolites may be made to coincide with either HTV positive or negative plasma, the extent of alteration required thus providing an indication of the relative amounts of metabolites present in the HIV positive or negative plasma FIG. 15 shows the emission profile of an HTV negative plasma sample (designated as 168 - a thin solid line), and that of a sample having a mixture of NADH, thiochrome, and albumin having proportions so that its mission profile (designated as 170 - a thin broken line) approximately matches that of the negative HIV plasma sample. FIG. 16 shows the emission profile of an HTV positive plasma sample (designated as 172 - a thin solid line), 0 and that of a sample having a mixture of NADH, thiochrome, and albumin having proportions so that its mission profile (designated as 174 - a thin broken line) approximately matches that of the negative HTV plasma sample. Referring to FIGS. 16A-D, applicants found that C-M (carboxy-methyl) Affi Gel Blue has a differential effect on HTV positive and negative plasmas. These results are obtained when specific ratios of plasma to C-M Affi Gel Blue are used. More specifically, in preparing CM-ABG treated samples, 0.25 milliliter (ml) of plasma is diluted to 2.0ml with 20mM of phosphate buffer and 1.5ml of CM-AGB, which yields consistent and noticeable shifts in the spectra For example, FIG. 16A shows the emission profiles of three 0 HIV positive plasma samples (broken lines designated as Pl, P2 and P3 sequentially from the top most broken line) and three HTV negative plasma samples (solid lines Nl, N2 and N3 from the top most solid line), all of which are whole plasma samples as control samples and are untreated with CM-ABG. FIG. 16B shows the same emission profiles of these _ . samples normalized at 550 nm. In comparison, referring to FIG. 16C, the emission profiles of CM-AGB treated HTV positive plasma samples (broken lines Pl, P2 and P3) and that of CM-AGB treated HTV negative plasma samples (solid lines Nl, N2 and N3) show much more differentiation between the HTV positive sample emission profiles and HTV negative sample emission profiles. Similarly, referring to FIG.16D which show emission profiles of 30 HTV positive samples treated with CM-AGB (broken lines Pl, P2 and P3) and emission profiles of HTV negative samples (solid lines Nl, N2 and N3), all normalized at 550 nm, the emission profiles for the CM-AGB treated samples normalized at 550 nm exhibit more differentiation between the emission profiles of the HTV positive samples and these of HTV 35 - 18 negative samples, than that of the HIV positive and negative samples untreated with CM-AGB. FIGS. 17A-D show emission profiles of another set of six samples, three of which are HIV positive samples and the other three samples are HTV negative samples. FIG. 17A shows the emission profiles of the six samples untreated with CM-AGB (with the three broken lines Pl, P2 and P3 for the HTV positive samples, and the three solid lines Nl, N2 and N3 for the HIV negative samples). The emission profiles for the same untreated samples normalized at 550 nm are shown in FIG. 17B. The mission profiles for the same samples treated with CM-AGB are shown in FIG. 17C (with the three broken lines Pl, P2 o and P3 for the HTV positive samples, and three solid lines Nl, N2 and N3 for the HTV negative samples). The emission profiles for the same CM-AGB treated samples normalized at 550 nm are shown in FIG. 17D, with the broken lines for the HTV positive samples and solid lines for the HTV negative samples. Again, the emission profiles obtained form the CM-AGB treated samples exhibit a much greater differentiation between the HTV 5 positive and negative samples than that obtained from samples untreated with CM-AGB. In summary, the differential effects of the CM-AGB on HTV positive and negative plasma suggest different plasma constituents have differential affinities for the CM-AGB gel and that these differences, as will be detailed below, are used as markers for HTV 0 positive plasma In accordance with the present invention, a method is provided to treat the plasma samples before obtaining fluorescence emission spectrums from the samples so that the emission spectrums, and more particularly, certain characteristics of the emission spectrums, from the samples infected with an infectious disease (e.g., HTV viruses) are more differentiable from those samples not infected with such disease. In a preferred embodiment for detecting HTV viruses, the samples are prepared using the following procedures and assay conditions. First, human plasma (0.75 ml) is diluted 1 :8 with 20mM potassium phosphate 0 buffer, pH 7.3. The diluted plasma is then filtered through nylon syringe filters of 0.45 micron (μm) pore size to remove particulate (protein and free lipid aggregates). The filtered and diluted plasma is divided into three aliquots. The first aliquot is left untreated and serves as a control sample, designated CT. The 5 second aliquot is chromatographed, preferably using 1.5 ml of carboxy-methyl Cibacron 19 Blue (C-M Affi Gel Blue, Bio Rad Laboratories) and is designated AGB. The third aliquot is adsorbed with 0.2ml of activated charcoal (Norit A) and designated CH. Each sample is then analyzed spectrofluorometrically using the system described above and illustrated in FIG. 1. In accordance with the present invention, spectrofluorimetry yields an emission spectra, the parameters of which is subsequently used to analyze each sample of plasma. To ensure the integrity and reproducibility of the emission spectra, applicants employed a beam compensation system which assures that all samples will be excited with identical levels of laser power. The circuit for this beam compensation system 0 which operates to control the total laser power is illustrated in FIGS. 2 A and 2B. The scan initiates laser power which increases over time. The shutter on the control device remains open until the power reaches a set point defined as V^ at which point the shutter closes. This enables the Infectious Disease LBS to control the total laser power used to excite the sample, yielding emission spectra which are internally compensated for input power. In accordance with the present invention, the analysis of a given sample's emission profile is performed using the parameters defined as follows and the algorithm described in detail below. The definitions of the parameters used in the algorithm are as follows: λ p : The wavelength in nanometers at which the peak of fluorescence intensity is 0 obtained. Mathematically, this is when dY/dX=0, where Y is the intensity of fluorescence and X is wavelength of the fluorescence. For example, λ^ is the peak wavelength of a control sample. Am: The amplitude of the peak fluorescence. For example, AΠI CT corresponds to the _ - amplitude of a control sample. Ar: The area ratio. The area ratio is defined as, as depicted in FIG. 18, the area under the emission spectrum extending from a first selected wavelength (λ 0 ) to a second selected wavelength (λ^), divided by the area under the curve extending the second selected wavelength to a third selected wavelength point(λ 0 ' ). Mathematically this will be calculated 30 as [Jxo ^/Ji n 01 ]. In the preferred embodiment as depicted in FIG. 18, 410 nm, 440 nm and 550 nm are selected as the first, second and third selected wavelengths, respectively. They are also used in all of the area ratio data shown herein. It should be understood that different wavelengths may be used, which may be adapted to obtain the same results as 35 described herein. 20 In accordance with the present invention, one or more of these parameters are used to discriminate samples infected with an infectious disease, such as HTV positive samples, from non-infected samples, such as HTV negative samples. For example, referring to FIG. 19, the amplitude, Am, is used to differentiate the HTV positive samples from the HTV negative samples. In FIG. 19, the x-axis corresponds to the sample number, and the y-axis corresponds to the amplitude, Am, of the samples normalized at 550 nm. For each sample, two measurements of the amplitude are performed and shown in the FIG., one for the untreated sample (i.e., control sample) which is shown as a back square in the FIG., the 1 o other for the sample treated with CM-AGB which is shown as a black circle in the FIG.. The measurements results designated "N" are obtained from known HTV negative samples, which are determined by commercially available, FDA-approved tests. The measurement results designated "P" are obtained from known HTV positive samples, which are determined by commercially available, FDA-approved tests. As shown in this FIG., sample Nos. 1, 2, 3, 7, 8 and 9 are known HTV negative samples, whereas sample Nos. 4, 5, 6, 10, 11 and 12 are known HTV positive samples. On the basis of the amplitude measurement results shown in FIG. 19, it is seen that the HTV negative samples and HTV positive samples can be discriminated on the basis of 20 their amplitudes, particularly the amplitudes (indicated as black circles in the FIG.) of the CM-AGB treated samples. For example, if a normalized amplitude value of 5 is used to discriminate the samples treated with CM-AGB (that is, the samples having an amplitude above 5 are deemed to be HTV positive whereas the samples having a normalized amplitude „ . less than 5 are deemed to be HTV negative), it is seen that the six HTV positive samples among the 12 samples tested will be correctly discriminated from the six HIV negative samples. It is noted that the CM-AGB treatment of the samples improves the discrimination of the infected samples from the uninfected samples. In accordance with the present invention, peak wavelength, λ p , is used to 30 discriminate infected samples, such as HTV positive samples, from uninfected samples, such as HIV negative samples. Referring to FIG. 20, which are the peak wavelength measurement results of the same set of samples that are used to obtain the amplitude measurements shown in FIG. 19, and which has the same designations, if a peak wavelength 35 of 435 nm is used to discriminate the CM-AGB treated HIV positive samples from the CM- 21 AGB treated HIV negative samples, it is seen that the six HIV positive samples among the 12 samples tested will be correctly discriminated from the six HIV negative samples. It is also noted that the CM-AGB treatment of the samples improves the discrimination of the infected samples from the uninfected samples for peak wavelength measurement. In accordance with the present invention, area ratio, Ar, is used to discriminate infected samples, such as HIV positive samples, from uninfected samples, such as HTV negative samples. Referring to FIG. 21, which are the area ratio measurement results of the same set of samples that are used to obtain the amplitude measurements shown in FIG. 19, an area ratio of 1.6 is used to discriminate the CM-AGB treated HTV positive samples from the CM-AGB treated HTV negative samples, the six HTV positive samples among the 12 samples tested will be correctly discriminated from the six HTV negative samples. It is clear from the test results that the CM-AGB treatment of the samples improves the discrimination of the infected samples from the uninfected samples. In accordance with the present invention, changes of the amplitudes of samples, ΔAm, before and after CM-AGB treatment, are used to discriminate infected samples, such as HTV positive samples, from uninfected samples, such as HTV negative samples. Referring to FIG.22, which shows the amplitude changes for the same set of samples that shown in FIG. 19, if no change of amplitude (i.e., ΔAm=0.0) is used to discriminate the HTV positive samples from the HTV negative samples, it is seen that the six HTV positive samples among the 12 samples tested will be correctly discriminated from the six HTV negative samples. In accordance with the present invention, changes of the peak wavelengths of samples, Δλ p before and after CM-AGB treatment, are used to discriminate infected samples, such as HTV positive samples, from uninfected samples, such as HTV negative samples. Referring to FIG. 23, which shows the amplitude changes for the same set of samples in FIG. 19, if no change of peak wavelength (i.e., Δλ p = 0.0 nm) is used to discriminate the HTV positive samples from the HTV negative samples, it is seen that HTV positive sample Nos. 4, 5, 6, 10, 11 and 12 will be discriminated from HIV negative sample Nos. 1, 2, 3 and 9. However, HTV negative sample Nos. 7 and 8 will not be discriminated from the HIV positive samples. - 22 - In accordance with the present invention, changes of area ratios of the of samples, ΔAm, before and after CM-AGB treatment, are used to discriminate infected samples, such as HTV positive samples, from uninfected samples, such as HIV negative samples. Referring to FIG. 24, which shows the area ratio changes for the same set of samples in FIG. 19, if no change of area ratio (i.e., ΔAr = 0.0) is used to discriminate the HTV positive samples from the HTV negative samples, HIV positive sample Nos. 4, 5, 6, 10, 11 and 12 will be discriminated from HTV negative sample Nos. 1, 2, 3 and 9, but HIV negative sample Nos. 7 and 8 will not be discriminated from the HIV positive samples. However, if 10 a change of area ratio of 0.2 (i.e., ΔAr = 0.2) used, all of the HTV positive samples will be discriminated from the HTV negative samples. In accordance with the present invention, although one of the above-mentioned parameters by itself may not be able to discriminate infected samples from uninfected samples with one hundred percent accuracy, if more than one of the parameters are used, high accuracy may nevertheless be achieved. In addition, proper algorithms using one or more of the above described parameters may be used to discriminate infected samples from non-infected samples. In accordance with the present invention, various discriminators are provided for 20 discriminating infected samples from non-infected samples. In a preferred embodiment, a discriminator Dl is constructed from 1/λ p , Am and Ar, all three of which will be greater for positive samples than negative samples or the mean value from a normal data base. Thus, any additive or multiplicative combination of these _ . parameters from positive samples divided by an identical combination of these parameters from the normal data base will be greater than 1. The value will be closer to 1 or less than 1 for negative samples. Such an analytic function for Dl is expressed as Dl = f(l/λ p , Am, Ar). Another discriminator D2 is provided, which takes advantage of the differential 30 shifts in these parameters (l/λ p , Am, Ar) after the sample undergoes chromatography through CM-Affi Gel Blue. After chromatography, Δλ p is greater for HIV positive samples than for HTV negative (normal) samples. Because ΔAm is greater for HIV negative samples than for HTV positive samples, the reciprocal of the difference in Am, 1/ΔAm, is greater for 35 positive samples. The parameter ΔAr is greater for positive samples. Thus, any additive or 23 multiplicative combination of these parameters from positive samples divided by an identical combination of these parameters from the normal data base will again be greater than 1. This ratio for negative samples will be closer 1 or less than 1. Such an analytic function for D2 is expressed as D2 = f(Δλ p , Δl/Am, ΔAr). Another discriminator D3 is provided, which will reflect the differential effects of adsorption by charcoal. The parameter 1/Δλ p will be greater for HTV negative samples than for HIV positive samples, so will be the parameter 1/ΔAr. Thus, any additive or multiplicative combination of these parameters divided by the same combination from the normal data base will be greater than 1 for positive samples and closer to 1 or less than 1 for HTV negative samples. Such an analytic function for D3 is described by D3 = f(Δλ p , 1/ΔAr). In accordance with the present invention, an aggregate discriminator D*=f (iDl, jD2,...,kD3 ) is provided, which will yield values for HTV positive samples greater than for HTV negative samples. The coefficients i through k are weighing factors to be determined empirically. HTV Negative samples will yield a range of D*s, the variance of which within the data base for the normal samples (i.e., HTV negative samples) must be determined. This will be determined from large scale testing by the Infectious Disease LBS of the present invention. FIG. 25 illustrates a flow diagram of the infectious disease detection method of the present invention. A plasma blood sample to be tested is first divided into three portions: The first portion is diluted 1 :8 with potassium phosphate buffer and will be used as a control sample (referred in the FIG. as "control"); the second portion is also diluted 1 :8 with potassium phosphate buffer and then chromatographed through CM-AGB (referred in the FIG. as "CM Column"); and the third portion is treated with activated charcoal (referred in the FIG. as "Cha Treatment"). After that, all three portions are provided to the LBS of the present invention to obtain their fluorospectrum in the desired wavelength band with excitation at a desired wavelength. Their fluorospectrum and characteristics and/or parameters are then used in an algorithm for calculation, which provides a final indicator as to whether or not the sample is infected with certain infectious diseases. The method and apparatus for infectious disease detection of the present invention may be used to detect HTV infection at a very early stage where it is still not detectable by - 24 - the widely used enzyme-linked immunosorbent assay method ("the ELISA method") or conventional clinical diagnosis. FIGS. 26A-C show the measurement results of the area ratio, peak amplitude, and peak wavelength, of the normal database (represented as "o" in the FIG.), respectively, and those of blood samples, untreated with CM-AGB or charcoal, (i.e., control samples) from a single individual at difference times at an early stage of HTV infection (represented as "+" in the FIG.). There are nine samples taken from the same individual and tested and their test results are arranged in the FIG. such that the left-most result is from the blood plasma sample first taken in time, and the right-most result from the blood plasma sample last taken in time, and the results in-between are arranged sequentially from the earlier-taken samples to the later-taken samples. As shown in FIGS. 26A-C, the test results of the blood samples from the HTV infected individual are fairly discriminated from those of the normal database. FIGS.27A-C are the measurement of the same parameters for the same samples after the samples are treated with CM-AGB. As shown, the discrimination between the results of the infected samples and those of the normal database is even more evident than the measurement on the untreated samples; the infected samples are clearly discriminated from the normal database. FIG.28 is a table listing the sample numbers, the relative time when the samples are taken, and their ELISA method test results, and conventional clinical diagnosis test results. For the first four samples, both the ELISA method and conventional clinical diagnosis fail to detect the HTV viruses. In comparison, as shown in FIGS. 26A-C and 27A-C, these four samples are discriminated from the normal database by using the method and apparatus of the present invention. Accordingly, the infectious disease detection method and apparatus of the present invention provide earlier detection of infection, such as HTV infection, when it is yet to be detectable by conventional detection means. In accordance with the present invention, the infectious disease detection method and apparatus of the present invention are used to discriminate Hepatitis A, B, and C. Referring to FIG. 29, the x-axis is the sample number and the y-axis is (Am BL -Amcπ), where Am BL is the peak amplitude of the emission spectrum for the AGB-treated sample and AmcH is the peak amplitude of the emission spectrum for the charcoal-treated samples. Sample Nos. 1-80 are samples from the normal database (i.e., Hepatitis negative samples). - 25 Sample Nos. 81-100 are samples known to be Hepatitis A positive. Sample Nos. 101-120 are samples known to be Hepatitis B positive. Sample Nos. 121-127 are samples known to be hepatitis C positive. As shown by this FIG., the parameter (Am BL -Amc H ) is a good discriminator between normal samples and hepatitis A or B positive samples. In addition, this parameter is also a discriminator, although not one hundred percent accurate, between Hepatitis A samples and Hepatitis C samples. FIG. 30 shows the parameter i^- icβ), i.e., area ratio difference between AGB- treated and charcoal-treated samples, for the same set of samples of FIG. 29. It is shown o that this parameter discriminates Hepatitis A and hepatitis C from normal samples. FIG. 31 shows the peak wavelength, cπ, measurement of charcoal-treated samples, which indicates that this parameter discriminates Hepatitis A, B and C, respectively, from the normal samples. FIG. 32 shows the parameter (Amc M -Amcr), i.e., peak amplitude differences between CM-AGB treated samples and non-treated samples (control samples), which indicate that this parameter discrirninates Hepatitis A, B and C, respectively, from the normal samples. Moreover, this parameter can also be used to differentiate Hepatitis A from Hepatitis C. 20 FIG. 33 shows the parameter ( CM - QJ ), i.e., peak wavelength differences between CM-AGB treated samples and charcoal-treated samples, which shows that this parameter distinguishes Hepatitis A and C from normal samples. FIG. 34 shows the parameter (Am,^ /λcπ), i.e., the amplitude of the CM-AGB _ - treated samples divided by the peak wavelength of the charcoal-treated samples, which demonstrate that this parameter is a partial discrirninator for Hepatitis A and C from normal samples, and is a good discriminator for Hepatitis B and normal samples. FIG. 35 shows a composite parameter (Ar CM *Am CM /λ CM ), i.e., the area ratio of the CM-AGB treated samples times the amplitude ofsuch CM-AGB treated samples divided by 30 the peak wavelength ofsuch CM-AGB treated samples, which differentiates Hepatitis A, B, and C from the normal samples. In all of the above samples, the laser excitation wavelength and the observed spectrum range are the same as that described above for the HTV detection. This 35 demonstrates that the infectious disease detection method and apparatus of the present 26 invention is capable of being adapted for detection of a variety of viruses present in plasma samples, such as HTV viruses, and Hepatitis A. B and C. It will be apparent to one of ordinary skill in the art that the various other parameters may be adapted in accordance with the present invention, which may be used to discriminate infectious diseases, such as Hepatitis A, B and C. The following examples provides additional parameters for detection of Hepatitis A, B and C. FIG. 36 shows the parameter of area ratios, Ar, for control samples, Ar CT , (i.e., non- treated samples), represented as small squares in the FIG.; CM-AGB treated samples, AT CM , represented as small circles in the FIG., and charcoal-treated samples, AT CH , represented as small triangles in the FIG.. It is shown that the parameter Ar CT is a good discrirninator for Hepatitis A, B and C, and the normal samples. FIG.37 shows the normalized peak amplitude, Am, for control samples, Amcr, (i.e., non-treated samples), represented as small squares in the FIG.; CM-AGB treated samples, Amc M , represented as small circles in the FIG., and charcoal-treated samples, Amcπ, represented as small triangles in the FIG. FIG. 38 shows the peak wavelength, λ P , for control samples, A CT , (i.e., non-treated samples), represented as small squares in the FIG.; CM-AGB treated samples, A CM , represented as small circles in the FIG., and charcoal-treated samples, Λ CH , represented as small triangles in the FIG.. FIG. 39 shows the area ratio changes between CM-AGB treated samples and control samples, (Arc M -Arcr), represented as small circles in the FIG.; and area ratio changes _ between charcoal treated samples and control samples, (AΓ CH -AT CΓ ), represented as small triangles in the FIG- FIG. 40 shows the peak amplitude changes between CM-AGB treated samples and control samples, (Amc M -Aπicr), represented as small circles in the FIG.; and peak amplitude changes between charcoal treated samples and control samples, (Amcπ-Anicr), represented 0 as small triangles in the FIG.. FIG. 41 shows the peak wavelength changes between CM-AGB treated samples and control samples, (λpc M -λpcr), represented as small circles in the FIG.; and peak wavelength changes between charcoal treated samples and control samples λpc H -λpcr), represented as 5 small triangles in the FIG.. - 27 FIG. 42 shows the area ratio changes between CM-AGB treated samples and charcoal-treated samples, (AT CM -AT CH ), represented as small circles in the FIG.. It clearly shows that this parameter is a good discriminator for normal samples and the samples containing Hepatitis A, B or C. FIG. 43 shows the amplitude changes between CM-AGB treated samples and charcoal-treated samples, (Amc M -Amc H ), represented as small circles in the FIG.. FIG.44 shows the peak wavelength changes between CM-AGB treated samples and charcoal-treated samples, (λpc M -λpcu), represented as small circles in the FIG.. This parameter clearly discriminates the normal samples from those containing Hepatitis A, B or C. FIG. 45 shows a composite parameter, area ratio times the amplitude divided by the peak wavelength, Ar CM *Am CM /λp CM , for samples treated with CM-AGB, represented as small circles in the FIG.. This parameter at least differentiates the normal samples from Hepatitis A or B positive samples. FIG.46 shows another composite parameter, area ratio times the amplitude divided by the peak wavelength, Ar CH *Am CH /λp CH , for samples treated with charcoal, represented as small circles in the FIG. The preferred embodiment described above is not intended to limit the applicability of the present invention. Rather, a person skilled in the art would appreciate that various modifications of the arrangements and types of components used in the detection system not mentioned in the specifications of the present invention would fall within the scope and _ spirit of the claimed invention. For instance, other types of spectrometers may be used in place of a CCD spectrometer. 0 5 28

Claims: We claim: 1. Method for detecting presence of an infection comprising: a., obtaining plasma; b. preparing a sample from the plasma; c. directing laser light of a predetermined wavelength onto the sample; d. obtaining an emission spectrum from the sample; and e. comparing the emission spectrum with a control spectrum to determine 10 the presence of the infection in the sample. 2. Method for detecting presence of an infection comprising: a. obtaining plasma; b. preparing a sample from the plasma; c. directing laser light of a wavelength between about 270 and 400 nanometers onto the sample; d. obtaining an emission spectrum from the sample; and e. comparing the emission spectrum with a control spectrum to determine 20 the presence of the infection in the sample. 3. Apparatus for detecting the presence of an infection in a sample comprising: a laser light source adapted to emit radiation of a predetermined _- wavelength; b. the laser light source being disposed so as to be capable of radiating the sample; c. optical detector being disposed relative to the laser light source to receive an emission radiation from the sample; 30 d. computer coupled to the optical detector to process the emission radiation into a signal representative of the sample and to compare the signal to a control signal to allow for deteπnination of presence of infection in the sample. 35 4. Apparatus for detecting an infection in a sample comprising: 29 a laser light source adapted to emit radiation at a wavelength between about 270 and 400 nanometers; b. the laser light source being disposed so as to be capable of radiating the sample; c. optical detector being disposed relative to the laser light source to receive an emission radiation from the sample; d. computer coupled to the optical detector to process the emission radiation into a signal representative of the sample and to compare the signal to a control signal to allow for determination of presence of infection in the sample. 30 -

Inventors: CANTER JOSEPH, SAPIRSTEIN VICTOR STEPHAN, YANG YONG WU, ZHOU WANG LONG, CANTER, JOSEPH, SAPIRSTEIN, VICTOR, STEPHAN, YANG, YONG, WU, ZHOU, WANG, LONG
Applicants: LASER MEDICAL CORP, LASER MEDICAL CORPORATION
Application year: 1999
Main classification: G01N15
IPC codes: C12Q1, G01N15, G01N21, G01N33, G01N35