USRE41333E1 - Multi-tier method of developing localized calibration models for non-invasive blood analyte prediction - Google Patents
Multi-tier method of developing localized calibration models for non-invasive blood analyte prediction Download PDFInfo
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Definitions
- the invention relates to non-invasive blood analyte predication using near IR tissue absorption spectra. More particularly, the invention relates to a method of classifying sample spectra into groups having a high degree of internal consistency to minimized prediction error due to spectral interferents.
- NIR near infrared
- Tissue layers each containing a unique heterogeneous chemistry and particulate distribution, result in light absorption and scattering of the incident radiation.
- T is a matrix representing the concentration or magnitude of interferents in all samples, and P represents the pure spectra of the interfering substances or effects present. Any spectral distortion can be considered an interferent in this formulation. For example, the effects of variable sample scattering and deviations in optical sampling volume must be included as sources of interference in this formulation.
- y GLS (K T — ⁇ 1 K) ⁇ 1 K T — ⁇ 1 (x ⁇ k 0 ) (8)
- _ is defined as the covariance matrix of the interfering substances or spectral effects
- ⁇ is defined as the measurement noise
- x is the spectral measurement
- k 0 is the instrument baseline component present in the spectral measurement.
- NIRI Imaging
- NIRS quantitation
- the invention provides a Multi-Tier method for classifying tissue absorbance spectra that localizes calibration and sample spectra into local groups that are used to reduce variation in sample spectra due to co-variation of spectral interferents, sample heterogeneity, state variation and structural variation.
- Measurement spectra are associated with localized calibration models that are designed to produce the most accurate estimates for the patient at the time of measurement. Classification occurs through extracted features of the tissue absorbance spectrum related to the current patient state and structure.
- the invention also provides a method of developing localized calibration models from tissue absorbance spectra from a representative population of patients or physiological states of individual patients that have been segregated into groups.
- the groups or classes are defined on the basis of structural and state similarity such that the variation in tissue characteristics within a class is smaller than the variation between classes.
- FIG. 1 provides a representation of a Multi-Tiered Classification Tree structure, according to the invention
- FIG. 2 is a block diagram of the architecture of an intelligent system for the noninvasive measurement of blood analytes, according to the invention
- FIG. 3 is a block diagram of a pattern classification system, according to the invention.
- FIG. 4 is a noninvasive absorbance spectrum collected using a diffuse reflectance NIR spectrometer
- FIG. 5 shows the spectra of repeated noninvasive measurements with no attempt to control tissue hydration
- FIG. 6 shows the spectra of repeated noninvasive measurements using ambient humidity to control hydration, according to the invention
- FIG. 7 shows a noninvasive absorbance spectrum having a pronounced fat band at 1710 nm
- FIG. 8 is a block schematic diagram of a general calibration system for mutually exclusive classes, according to the invention.
- FIG. 9 is a block schematic diagram of a general calibration system for fuzzy class assignments, according to the invention.
- FIG. 10 is a block schematic diagram showing an example of parallel calibration models for fuzzy set assignments, according to the invention.
- the classification of tissue samples using spectra and other electronic and demographic information can be approached using a wide variety of algorithms.
- a wide range of classifiers exists for separating tissue states into groups having high internal similarity: for example, Bayesian classifiers utilizing statistical distribution information; or non-parametric neural network classifiers that assume little a priori information. See K. Funkunaga, Intro to Statistical Pattern Recognition, Academic Pres, San Diego, Calif. (1990); and J. Hertz, A. Krogh, R. Palmer, Introduction To The Theory Of Neural Computation, Addison-Wesley Publishing Co., Redwood City, Calif. (1991).
- the multi-tiered classification approach selected here provides the opportunity to grow and expand the classification database as more data become available.
- the multi-tiered classifier is similar to a hierarchic classification tree, but unlike a classification tree, the decision rules can be defined by crisp or fuzzy functions and the classification algorithm used to define the decision rule can vary throughout the tree structure.
- a first tier 11 assigns sample spectra according to pre-defined age groups: 18-27 (15), 28-40 (14), 40-54 (13) and 55-80 years old (12). As indicated, a sample has been assigned to the 28-40 age group.
- a second tier 16 assigns samples to classes 18, 17 according to sex, in this case female.
- a third tier 19 groups according to stratum corneum hydration: 31-60 (20); ⁇ 30 (21) and >61 corneometer units (22); in this case, >61.
- a fourth tier 23 groups according to skin temperature: 88-90 (24); 86-88 (25); 84-86 and ⁇ 84 degrees; in this case 84-86 degrees. In this way, a determination of class membership is made within each tier in the multi-tiered structure. Finally, in a last tier 28 , a final class assignment is made into one of three pre-defined groups 29, 30 and 31 according to relative optical thickness of the dermis.
- classification is made based on a priori knowledge of the sample, or on the basis of instrumental measurements made at the tissue measurement site.
- the first two tiers utilize a priori information about the sample: subject age and sex.
- Successive tiers utilize information gained from instrumental measurements at the tissue measurement site. Further classification occurs on the basis of extracted features from the tissue absorbance spectra themselves.
- FIG. 2 shows a block diagram of an intelligent measurement system for noninvasive blood analyte prediction, fully described in the parent application to the current application: S. Malin and T. Ruchti, An Intelligent System For Noninvasive Blood Analyte Prediction, U.S. patent application Ser. No. 09/359,191; Jul. 22, 1999,
- the purpose of feature extraction 41 in FIG. 2 is to concisely represent the structural properties and physiological state of the tissue measurement site.
- the set of features is used to classify the patient and determine the calibration model(s) most useful for blood analyte prediction.
- the dimension, M i indicates whether the i th feature is a scalar or a vector and the aggregation of all features is the vector z. When a feature is represented as a vector or a pattern, it exhibits a certain structure indicative of an underlying physical phenomenon.
- Abstract features do not necessarily have a specific interpretation related to the physical system. Specifically, the scores of a principal component analysis are useful features although their physical interpretation is not always known.
- the utility of the principal component analysis is related to the nature of the tissue absorbance spectrum. The most significant variation in the tissue spectral absorbance is not caused by a blood analyte but is related to the state, structure and composition of the measurement site. This variation is modeled by the primary principal components. Therefore, the leading principal components tend to represent variation related to the structural properties and physiological state of the tissue measurement site.
- Simple features are derived from an a priori understanding of the sample and can be related directly to a physical phenomenon. Useful features that can be calculated from NIR spectral absorbance measurements include but are not limited to:
- Spectral decomposition is employed to determine the features related to a known spectral absorbance pattern.
- Protein and fat for example, have known absorbance signatures that can be used to determine their contribution to the tissue spectral absorbance.
- the measured contribution is used as a feature and represents the underlying variable through a single value.
- the goal of feature extraction is to define the salient characteristics of measurements that are relevant for classification. Feature extraction is performed at branching junctions of the multi-tiered classification tree structure.
- the goal of the classification step is to assign the calibration model(s) most appropriate for a particular noninvasive measurement. In this step the patient is assigned to one of many predefined classes for which a calibration model has been developed and tested. Since the applied calibration model is developed for similar tissue absorbance spectra, the blood analyte predictions are more accurate than those obtained from a universal calibration model.
- pattern classification generally involves two steps:
- Class definition is the assignment of the measurements in the exploratory data set to classes. After class definition, the measurements and class assignments are used to determine the mapping from the features to class assignments.
- Class definition is performed through either a supervised or an unsupervised approach. See Y. Pao, Adaptive Pattern Recognition and Neural Networks, Addison-Wesley Publishing Co., Reading, Mass. (1989).
- supervised classes are defined through known differences in the data.
- the use of a priori information in this manner is the first step in supervised pattern recognition, which develops classification models when the class assignment is known. For example, the majority of observed spectral variation can be modeled by three abstract factors, which are related to several physical properties including body fat, tissue hydration and skin thickness. Categorizing patients on the basis of these three features produces eight different classes if each feature is assigned a “high” and “low” value.
- the drawback to this approach is that attention is not given to spectral similarity and the number of classes tends to increase exponentially with the number of features.
- Unsupervised methods rely solely on the spectral measurements to explore and develop clusters or natural groupings of the data in feature space. Such an analysis optimizes the within cluster homogeneity and the between cluster separation. Clusters formed from features with physical meaning can be interpreted based on the known underlying phenomenon causing variation in the feature space. However, cluster analysis does not utilize a priori information and can yield inconsistent results.
- a combination of the two approaches utilizes a priori knowledge and exploration of the feature space for naturally occurring spectral classes.
- classes are first defined from the features in a supervised manner. Each set of features is divided into two or more regions and classes are defined by combinations of the feature divisions.
- a cluster analysis is performed on the data and the results of the two approaches are compared. Systematically, the clusters are used to determine groups of classes that can be combined. After conglomeration, the number of final class definitions is significantly reduced according to natural divisions in the data.
- a classifier is designed through supervised pattern recognition. A model is created, based on class definitions, that transforms a measured set of features to an estimated classification. Since the ultimate goal of the classifier is to produce robust and accurate calibration models, an iterative approach must be followed in which class definitions are optimized to satisfy the specifications of the measurement system.
- the statistical classification methods are applied to mutually exclusive classes whose variation can be described statistically. See J. Bezdek, S. Pal, eds, Fuzzy Models for Pattern Recognition, IEEE Press, Piscataway, N.J. (1992).
- classifier is designed by determining an optimal mapping or transformation from the feature space to a class estimate which minimizes the number of misclassifications.
- the form of the mapping varies by method as does the definition of “optimal”.
- Existing methods include linear Discriminant analysis, SIMCA, k nearest-neighbor and various forms of artificial neural networks.
- the class is used to select or adapt the calibration model as discussed in the Calibration Section. Fuzzy Classification
- a more versatile method of class assignment is based on fuzzy set theory. See Bezdek, et al., supra; and C. Chen, ed., Fuzzy Logic and Neural Network Handbook, IEEE Press, Piscataway, N.J. (1996); and L. Zadeh, Fuzzy Sets, Inform. Control, vol. 8, pp. 338-353 (1965).
- membership in fuzzy sets is defined by a continuum of grades and a set of membership functions that map the feature space into the interval [0,1] for each class.
- the assigned membership grade represents the degree of class membership with “1” corresponding to the highest degree. Therefore, a sample can simultaneously be a member of more than one class.
- the membership vector provides the degree of membership in each of the predefined classes and is passed to the calibration algorithm.
- fuzzy class definitions similar to the methods previously described. Fuzzy cluster analysis can be applied and several methods, differing according to structure and optimization approach can be used to develop the fuzzy classifier. All methods attempt to minimize the estimation error of the class membership over a population of samples.
- Blood analyte prediction occurs by the application of a calibration model to the preprocessed measurement as depicted in FIG. 2 .
- the proposed prediction system involves a calibration or a set of calibration models that are adaptable or selected on the basis of the classification step.
- Accurate blood analyte prediction requires calibration models that are capable of compensating for the co-varying interferents, sample heterogeneity, state and structural variations encountered. Complex mixtures of chemically absorbing species that exhibit substantial spectral overlap between the system components are solvable only with the use of multivariate statistical models. However, prediction error increases with increasing variation in interferents that also co-vary with analyte concentration in calibration data. Therefore, blood analyte prediction is best performed on measurements exhibiting smaller interference variations that correlate poorly with analyte concentration in the calibration set data. Since it may not be possible to make all interference variations random, it is desirable to limit the range of spectral interferent variation in general.
- the principle behind the multi-tiered classification and calibration system is based on the properties of a generalized class of algorithm that are required to compensate for overlapped interfering signals in the presence of the desired analyte signal. See H. Martens, T. Naes, Multivariate Calibration, John Wiley and Sons, New York (1989).
- the models used in this application require the measurement of multiple independent variables, designated as x, to estimate a single dependent variable, designated as y.
- y may be tissue glucose concentration
- x may represent a vector, [x 1 x 2 . . . x i ], consisting of the noninvasive spectrum signal intensities at each of n wavelengths.
- Equation 4 The generalized form of a model to be used in the calculation of a single glucose estimate uses a weighted summation of the noninvasive spectrum as in Equation 4.
- the weights, w are referred to as the regression vector.
- y ⁇ w i x i (4)
- the modeling error that might be expected in a multivariate system using Equation 5 can be estimated using a linear additive mixture model.
- Linear additive mixtures are characterized by the definition that the sum of the pure spectra of the individual constituents in a mixture equals the spectra of the mixture.
- Linear mixture models are useful in assessing the general limitations of multivariate models that are based on linear additive systems and those, noninvasive blood analysis, for example, that can be expected to deviate somewhat from linear additive behavior.
- FIG. 4 shows an exemplary noninvasive absorbance spectrum.
- a set of spectral measurements may be represented as a matrix X where each row corresponds to an individual sample spectrum and each column represents the signal magnitude at a single wavelength.
- the measurement matrix can be represented as a linear additive mixture model with a matrix of instrument baseline variations B 0 , a matrix of spectra of the pure components K, and the concentrations of the pure components, Y, and random measurement noise present in the measurement of each spectrum, E.
- X B 0 +YK T +E (6)
- the linear additive model can be broken up further into interferents and analytes as an extended mixture model.
- X B 0 +YK T +TP T +E (7)
- T is a matrix representing the concentration or magnitude of interferents in all samples, and P represents the pure spectra of the interfering substances or effects present. Any spectral distortion can be considered an interferent in this formulation. For example, the effects of variable sample scattering and deviations in optical sampling volume must be included as sources of interference in this formulation.
- MSE mean squared error
- Equation 10 describes the generalized limitations of least squares predictors in the presence of interferents. If K represents the concentrations of blood glucose, a basic interpretation of Equation 10 is: the mean squared error in glucose estimates increases with increased variation in interferences that also co-vary with glucose concentration in calibration data. Therefore, the accurate estimation of glucose is best performed on measurements exhibiting smaller interference variations that poorly correlate with glucose concentration in the calibration set data. Since it may not be possible to make all interference variations random with glucose, it is desirable to limit the range of spectral interference variation in general.
- the Multi-Tier Classification provides a method for limiting variation of spectral interferents by placing sample measurements into groups having a high degree of internal consistency.
- Tissue parameters to be utilized in class definition may include: stratum corneum hydration, tissue temperature, and dermal thickness.
- the stratum corneum (SC), or horny cell layer covers about 10-15 ⁇ m thickness of the underside of the arm.
- the SC is composed mainly of keratinous dead cells, water and some lipids. See D. Bommannan, R. Potts, R. Guy, Examination of the Stratum Corneum Barrier Function In Vivo by Infrared Spectroscopy, J. Invest. Dermatol., vol. 95, pp 403-408 (1990). Hydration of the SC is known to vary over time as a function of room temperature and relative humidity. See J. Middleton, B. Allen, Influence of temperature and humidity on stratum corneum and its relation to skin chapping, J. Soc. Cosmet. Chem., vol. 24, pp.
- the temperature of the measured tissue volume varies from the core body temperature, at the deepest level of penetration, to the skin surface temperature, which is generally related to ambient temperature, location and the amount of clothing at the tissue measurement site.
- the spectrum of water, which comprises about 65% of living human tissue is the most dominant spectral component at all depths sampled in the 1100-2500 nm wavelength range.
- the first tissue layer under the skin is the subcutaneous adipose tissue, consisting mainly of fat.
- the strength of the fat absorbance band can be used to assess the relative photon flux that has penetrated to the subcutaneous tissue level.
- a more pronounced fat band means that a greater photon flux has reached the adipose tissue and returned to the detector.
- FIG. 7 spectra with pronounced 71 and normal 72 fat bands are presented.
- the most important use of the optical thickness is to assess the degree of hydration in the interior tissue sampled by the optical probe.
- Optical thickness may also be a strong function of gender and body type, therefore this property measurement would be useful for assessing interior hydration states within a single individual.
- the designated classification is passed to a nonlinear model that provides a blood analyte prediction based on the patient classification and spectral measurement.
- This process illustrated in FIG. 8 , involves the modification of the estimation strategy for the current subject according to the structural tissue properties and physiological state manifested in the absorbance spectrum.
- This general architecture necessitates a nonlinear calibration model 101 such as nonlinear partial least squares or artificial neural networks since the mapping is highly nonlinear.
- a different calibration is realized for each class.
- the estimated class is used to select one of p calibration models most appropriate for blood analyte prediction using the current measurement.
- k is the class estimate for the measurement
- the calibrations are developed from a set of exemplar absorbance spectra with reference blood analyte values and pre-assigned classification definitions. This set, denoted the “calibration set”, must have sufficient samples to completely represent the range of physiological states to be encountered in the patient population.
- the p different calibration models are developed individually from the measurements assigned to each of the p classes. The models are realized using known methods including principal component regression, partial least squares regression and artificial neural networks. See Hertz, et al., supra; and Pao, supra; and Haykin, supra; and Martens, et al., supra; and N. Draper, H. Smith, Applied Regression Analysis, 2 nd ed., John Wiley and Sons, New York (1981).
- the various models associated with each class are evaluated on the basis of an independent test set or cross validation and the “best” set of models are incorporated into the Multi-tier Classification. Each class of patients then has a calibration model specific to that class.
- the calibration is passed a vector of memberships rather than a single estimated class.
- the vector, c is utilized to determine an adaptation of the calibration model suitable for blood analyte prediction or an optimal combination of several blood analyte predictions.
- the membership vector and the preprocessed absorbance spectrum are both used by a single calibration 111 for blood analyte prediction.
- the preferred realization, shown in FIG. 10 has separate calibrations 121 for each class. However, each calibration is generated using all measurements in the calibration set by exploiting the membership vector assigned to each measurement. In addition, the membership vector is used to determine an optimal combination of the p blood analyte predictions from all classes through defuzzification 122 . Therefore, during calibration development, a given measurement of the calibration set has the opportunity to impact more than one calibration model. Similarly, during prediction more than one calibration model is used to generate the blood analyte estimate.
- Each of the p calibration models is developed using the entire set of calibration data. However, when the k th calibration model is calculated, the calibration measurements are weighted by their respective membership in the k th class. As a result, the influence of a sample on the calibration model of a particular class is a function of its membership in the class.
- an iterative method such as artificial neural networks
- the membership is used to determine the frequency the samples are presented to the learning algorithm.
- an extended Kalman filter is applied with a covariance matrix scaled according to V.
- defuzzification is a mapping from the vector of blood analyte predictions and the vector of class memberships to a single analyte prediction.
- Existing methods of defuzzification such as the centroid or weighted average, are applied for small calibration sets. However, if the number of samples is sufficient, d(•) is generated through a constrained nonlinear model.
- the Multi-tiered Classification and Calibration is implemented in a scanning spectrometer which determines the NIR absorbance spectrum of the subject forearm through a diffuse reflectance measurement.
- the instrument employs a quartz halogen lamp, a monochromator, and InGaAs detectors.
- the detected intensity from the sample is converted to a voltage through analog electronics and digitized through a 16-bit A/D converter.
- the spectrum is passed to the Intelligent Measuring System (IMS) for processing and results in either a glucose prediction or a message indicating an invalid scan.
- IMS Intelligent Measuring System
Abstract
Description
yGLS=(KT — −1K)−1KT — −1(x−k0) (8)
where _ is defined as the covariance matrix of the interfering substances or spectral effects, Û is defined as the measurement noise, x is the spectral measurement, and k0 is the instrument baseline component present in the spectral measurement.
-
- 1. Co-variation of spectrally interfering species. The near infrared spectral absorption profiles of blood analytes tend to overlap and vary simultaneously over brief time periods. This overlap leads to spectral interference and necessitates the measurement of absorbance at more independently varying wavelengths than the number of interfering species.
- 2. Sample heterogeneity. The tissue measurement site has multiple layers and compartments of varied composition and scattering. The spectral absorbance versus wavelength measurement is related to a complex combination of the optical properties and composition of these tissue components. Therefore, the spectral response with changing blood analyte concentration is likely to deviate from a simple linear model.
- 3. State Variations. Variations in the subject's physiological state effect the optical properties of tissue layers and compartments over a relatively short period of time. Such variations, for example, may be related to hydration levels, changes in the volume fraction of blood in the tissue, hormonal stimulation, skin temperature fluctuations and blood hemoglobin levels. Subtle variations may even be expected in response to contact with an optical probe.
- 4. Structural Variations. The tissue characteristics of individuals differ as a result of factors that include hereditary, environmental influences, the aging process, sex and body composition. These differences are largely anatomical and can be described as slowly varying structural properties producing diverse tissue geometry. Consequently, the tissue of a given subject may have distinct systematic spectral absorbance features or patterns that can be related directly to specific characteristics such as dermal thickness, protein levels and percent body fat. While the absorbance features may be repeatable within a patient, the structural variations in a population of patients may not be amenable to the use of a single mathematical calibration model. Therefore, differences between patients are a significant obstacle to the noninvasive measurement of blood analytes through NIR spectral absorbance.
z=f(λ,x) (1)
where f: N→RM is a mapping from the measurement space to the feature space. Decomposing f(•) will yield specific transformations, fi(•): N→ M i for determining a specific feature. The dimension, Mi, indicates whether the ith feature is a scalar or a vector and the aggregation of all features is the vector z. When a feature is represented as a vector or a pattern, it exhibits a certain structure indicative of an underlying physical phenomenon.
-
- 1. abstract and
- 2. simple.
-
- 1. Thickness of adipose tissue. See J. Conway, K. Norris, C. Bodwell, A new approach for the estimation of body composition: infrared interactance, The American Journal of Clinical Nutrition, vol. 40, pp. 1123-1140 (December 1984) and S. Homma, T. Fukunaga, A. Kagaya, Influence of adipose tissue thickness in near infrared spectroscopic signals in the measurement of human muscle, Journal of Biomedical Optics, vol.1(4), pp. 418-424 (October 1996).
- 2. Tissue hydration. See K. Martin, Direct measurement of moisture in skin by NIR spectroscopy, J. Soc. Cosmet. Chem., vol. 44, pp. 249-261 (September/October 1993).
- 3. Magnitude of protein absorbance. See J. Conway, et al., supra.
- 4. Scattering properties of the tissue. See A. Profio, Light transport in tissue, Applied Optics, vol. 28(12), pp. 2216-2222 (June 1989) and W. Cheong, S. Prahl, A. Welch, A review of the optical properties of biological tissues, IEEE Journal of Quantum Electronics, vol. 26(12), pp. 2166-2185 (December 1990); and R. Anderson, J. Parrish. The optics of human skin, Journal of Investigative Dermatology, vol. 77(1), pp. 13-19 (1981).
- 5. Skin thickness. See Anderson, et al., supra; and Van Gemmert, et al., supra.
- 6. Temperature related effects. See Funkunga, supra.
- 7. Age related effects. See W. Andrew, R. Behnke, T. Sato, Changes with advancing age in the cell population of human dermis, Gerontologia, vol. 10, pp. 1-19 (1964/65); and W. Montagna, K. Carlisle, Structural changes in aging human skin, The Journal of Investigative Dermatology, vol. 73, pp. 47-53 (1979; and 19 J. Brocklehurst, Textbook of Geriatric Medicine and Gerontology, pp.593-623, Churchill Livingstone, Edinburgh and London (1973).
- 8. Spectral characteristics relates to sex. See T. Ruchti, Internal Reports and Presentations, Instrumentation Metrics, Inc.
- 9. Pathlength estimates. See R. Anderson, et al., supra and S. Matcher, M. Cope, D. Delpy, Use of water absorption spectrum to quantify tissue chromophore concentration changes in near-infrared spectroscopy, Phys.
- Med. Biol., vol. 38, pp. 177-196 (1993).
- 10. Volume fraction of blood in tissue. See Wilson, et al., supra.
- 11. Spectral characteristics related to environmental influences.
-
- 1. a mapping step in which a
classification model 53 measures the similarity of the extracted features to predefined classes; and - 2. an assignment step in which a
decision engine 54 assigns class membership. Within this framework, two general methods of classification are proposed. The first uses mutually exclusive classes and therefore assigns each measurement to one class. The second scheme utilizes a fuzzy classification system that allows class membership in more than one class simultaneously. Both methods rely on previously defined classes, as described below.
Class Definition
- 1. a mapping step in which a
c=f(z) (2 1)
where c is an integer on the interval [1,P] and P is the number of classes. The class is used to select or adapt the calibration model as discussed in the Calibration Section.
Fuzzy Classification
ck=fk(z) (2)
where k=1,2, . . . P, fk(•) is the membership function of the kth class, ckε[0,1] for all k and the vector cε P is the set of class memberships. The membership vector provides the degree of membership in each of the predefined classes and is passed to the calibration algorithm.
y=Σw
w=(XTX)−1XTyW. (5)
X=B0+YKT+E (6)
X=B0+YKT+TPT+E (7)
yGLS=(KTΣ−1K)−1KTΣ−1(x−k0); (8)
where Σ is defined as the covariance matrix of the interfering substances or spectral effects, ó is defined as the measurement noise, x is the spectral measurement, and k0 is the instrument baseline component present in the spectral measurement.
Σ=PT(ttT)−1P+diag(ó2) (9)
MSE(yGLS)=trace(KTΣ−1K)−1 (10)
ŷ=g(c,x) (11)
where g(•) is a nonlinear calibration model which maps x and c to an estimate of the blood analyte concentration, ŷ.
ŷ=gk(x), (12)
where gk(•) is the calibration model associated with the kth class.
ŷ=g(c,x) (13)
where g(•) is a nonlinear mapping determined through nonlinear regression, nonlinear partial least squares or artificial neural networks. The mapping is developed from the calibration set described previously and is generally complex.
F=XkM, (14)
where M is the matrix of the first n eigenvectors of P. The weighted covariance matrix P is determined through
P=XkVXk T, (15)
where V is a square matrix with the elements of Ck on the diagonal. The regression matrix, B, is determined through
B=(FTVF)−1FTVY. (16)
ŷ=d(c,[y1y2y3 . . . yp]), (17)
where d(•) is the defuzzification function, c is the class membership vector and yk is the blood analyte prediction of the kth calibration model. Existing methods of defuzzification, such as the centroid or weighted average, are applied for small calibration sets. However, if the number of samples is sufficient, d(•) is generated through a constrained nonlinear model.
INSTRUMENT DESCRIPTION
Claims (68)
z=f(λ,x)
W=(XTX)−1XTy,
z=f(λ,x)
W=(X T X)−1 X T Y,
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