Analyte system and method for determining hemoglobin parameters in whole blood

Abstract

A system of measuring hemoglobin and bilirubin parameters in a whole blood sample using optical absorbance. The system includes an optical-sample module, a spectrometer module, an optical fiber module optically connecting the optical-sample module to the spectrometer module, and a processor module. The optical-sample module has a light-emitting module having a LED light source, a cuvette and a calibrating-light module. The processor module receives and processes an electrical signal from the spectrometer module and transforms the electrical signal into an output signal useable for displaying and reporting hemoglobin parameter values and/or total bilirubin parameter values for the whole blood sample.

Claims

1. An optical absorbance measurement system for whole blood, the system comprising: an optical-sample module comprising: a light-emitting module having a LED light source capable of emitting light wherein the light is directed thereby defining an optical path; a replaceable cuvette module adjacent the light-emitting module wherein the replaceable cuvette module is adapted for receiving a whole-blood sample and has a sample receiving chamber with a first cuvette window and a second cuvette window aligned with the first cuvette window wherein the sample receiving chamber is disposed in the optical path for receiving light from the LED light source; a first optical diffuser positioned within the optical path between the LED light source and the replaceable cuvette module; and a second optical diffuser positioned within the optical path after the replaceable cuvette module; an optical fiber having a light-receiving end and a light-emitting end, the light-receiving end optically connected to the optical-sample module wherein the light-receiving end receives the light emitted along the optical path and conducts the light to the light-emitting end; a spectrometer module capable of receiving the light from the light-emitting end of the optical fiber, separating the light into a plurality of light beams wherein each light beam has a different wavelength, and converting the plurality of light beams into an electrical signal; and a processor module capable of receiving and processing the electrical signal from the spectrometer module generated for the whole-blood sample and transforming the electrical signal into an output signal useable for displaying and reporting hemoglobin parameter values and/or total bilirubin parameter values for the whole-blood sample.

2. The optical absorbance measurement system of claim 1 wherein the light-emitting module includes a plurality of optical components disposed in the optical path between the LED light source and the replaceable cuvette module, the plurality of optical components includes at least the first optical diffuser and one or more of a collimating lens, a circular polarizer, and a focusing lens.

3. The system of claim 1 wherein the calibrating-light module includes a beam splitter disposed in the optical path, the beam splitter capable of transversely receiving the one or more known wavelengths of light from the calibrating-light source and directing the one or more known wavelengths of light along the optical path.

4. The system of claim 3 wherein the second optical diffuser is disposed in the optical path downstream from the replaceable cuvette module but upstream from the beam splitter.

5. The system of claim 1 wherein the calibrating-light module includes a collimating lens disposed in the optical path between the replaceable cuvette module and the second optical diffuser.

6. The system of claim 1 wherein the spectrometer module comprising: an input slit positioned in the optical path to receive the light emitted from the light-emitting end of the optical fiber and to transmit the light therethrough; a prism disposed in the optical path wherein the prism is capable of receiving the light transmitted through the input slit, separating the light into a plurality of light beams wherein each light beam has a different wavelength, and re-directing the plurality of light beams back toward but offset from the input slit; and a light-array detector capable of receiving the plurality of light beams and converting the plurality of light beams into the electrical signal.

7. The system of claim 6 wherein the prism has a reflective back surface.

8. The system of claim 6 wherein the spectrometer module includes a thermal-compensating lens disposed in the optical path between the input slit and the prism and capable of substantially simultaneously transmitting the light from the input slit and the plurality of light beams from the prism.

9. The system of claim 8 wherein the thermal-compensating lens has a lens mount with a fixed mount end and an unfixed mount end, the fixed mount end being attached to a baseplate and wherein the lens mount has a coefficient of expansion greater than the coefficient of expansion of the baseplate.

10. The system of claim 6 wherein the light-array detector and the input slit are mounted on the same substrate adjacent each other.

11. The system of claim 1 wherein the processor module includes a micro-processor module, a memory module, and a function that maps hemoglobin parameter values and total bilirubin values to known blood levels in the memory module that is processed by the micro-processor module wherein the micro-processor module converts a digital signal received from a converter module into measured values wherein the measured values are proportional to the hemoglobin parameters and total bilirubin of a whole blood sample disposed in and being measured in the disposable cuvette placed in the optical path.

12. The system of claim 11 wherein the function that maps hemoglobin parameter values and total bilirubin values to known blood levels is generated from a plurality of hemoglobin parameter values and total bilirubin values of samples having known hemoglobin parameter and total bilirubin values for a predefined configuration of the sample receiving chamber.

13. The system of claim 11 wherein the function that maps hemoglobin parameter values and total bilirubin values to known blood levels is based on a kernel-based orthogonal projection to latent structures function.

14. The system of claim 6 wherein the prism is a Littrow prism.

15. The system of claim 14 wherein the Littrow prism has a reflective coating on a side opposite a ninety degree angle of the Littrow prism.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0049] FIG. 1 is a simplified, perspective view of one embodiment of the present invention showing a compact COOx subsystem.

[0050] FIG. 2 is a side elevation view of one embodiment of an optical-sample module shown in FIG. 1.

[0051] FIG. 3 is a front, perspective view of one embodiment of a light-emitting module of the optical-sample module shown in FIG. 2.

[0052] FIG. 3A is a front, perspective view of the light-emitting module shown in FIG. 3 showing a plurality of optical components.

[0053] FIG. 3B is an enlarged, side elevation view of the optical components shown in FIG. 3A.

[0054] FIG. 4 is a front perspective view of one embodiment of a cuvette assembly of the optical-sample module shown in FIG. 1.

[0055] FIG. 5 is a rear perspective view of the cuvette assembly shown in FIG. 4.

[0056] FIG. 6 is a front elevation view of a cuvette module of the cuvette assembly showing fluid input and output ports, a sample receiving chamber, a sample window, and an electronic chip assembly.

[0057] FIG. 7 is a rear perspective view of the sample receiving chamber of FIG. 6 showing cuvette first and second windows.

[0058] FIG. 8 is a rear plan view of the sample receiving chamber showing the electronic chip assembly disposed adjacent the sample receiving chamber.

[0059] FIG. 9 is a perspective view of one embodiment of a calibrating light module of the optical-sample module of FIG. 1.

[0060] FIG. 10 is a side cross-sectional view of the calibrating light module of FIG. 8 showing a calibrating light source.

[0061] FIG. 11 is a simplified, side plan view of the calibrating light source of the calibrating light module of FIG. 9 showing a plurality of optical components.

[0062] FIG. 12 is a front perspective view of one embodiment of a spectrometer module of FIG. 1 with a cover removed showing the internal components.

[0063] FIG. 13 is a rear perspective view of the spectrometer module of FIG. 12 showing an input light slit and adjacent light-array detector.

[0064] FIG. 14 is a rear cross-sectional view of the spectrometer module of FIG. 12 showing a single circuit board and the location of the input light slit and the light-array detector.

[0065] FIG. 15 is a top view of the spectrometer module of FIG. 12 showing the optical components with superimposed ray trace.

[0066] FIG. 16 is a ray trace showing the input light from the input light slit and a plurality of light beams refracted onto the light-array detector.

[0067] FIG. 17A is a perspective view of one embodiment of a thermal-compensating means for the spectrometer module showing insulation wrapped around the spectrometer module.

[0068] FIG. 17B is a perspective view of another embodiment of a thermal-compensating means for the spectrometer module showing a temperature controlling assembly.

[0069] FIG. 17C is a cross-sectional view of one embodiment of a lens mount of the spectrometer module of FIG. 12 showing a temperature-compensating lens mount.

[0070] FIG. 18 is a cross-sectional view of one embodiment of a lens mount of the spectrometer module of FIG. 12 showing a fixed lens mount.

[0071] FIG. 19 is a graphic illustration showing the correlation results of the COOx analyzer subsystem of the present invention for total hemoglobin using a K-OPLS mapping function and method.

[0072] FIG. 20 is a graphic illustration showing the correlation results of the COOx analyzer subsystem of the present invention for oxyhemoglobin using a K-OPLS mapping function and method.

[0073] FIG. 21 is a graphic illustration showing the correlation results of the COOx analyzer subsystem of the present invention for carboxyhemoglobin using a K-OPLS mapping function and method.

[0074] FIG. 22 is a graphic illustration showing the correlation results of the COOx analyzer subsystem of the present invention for deoxyhemoglobin using a K-OPLS mapping function and method.

[0075] FIG. 23 is a graphic illustration showing the correlation results of the COOx analyzer subsystem of the present invention for methemoglobin using a K-OPLS mapping function and method.

[0076] FIG. 24 is a graphic illustration showing the correlation results of the COOx analyzer subsystem of the present invention for total bilirubin using a K-OPLS mapping function and method.

DETAILED DESCRIPTION

[0077] Embodiments of the present invention are illustrated in FIGS. 1-24. FIG. 1 shows one embodiment of a COOx analyzer subsystem 10. COOx analyzer subsystem 10 includes at least an optical-sample module 20, an optical fiber 90 and a spectrometer module 100. COOx analyzer subsystem 10 may optionally include a processor module 150 or processor module 150 may optionally be included in an electronics circuit of a diagnostic system in which the COOx analyzer subsystem 10 is a part. Line 5 is included to signify that the processor module 150 may or may not be part of the COOx subsystem 10. Processor module 150 includes, but is not limited to a microprocessor module 152 and a memory module 154. Optionally, the processor module 150 may also include a converter module 156 or converter module 156 may be external to the COOx analyzer subsystem 10. COOx analyzer subsystem 10 is used to measure the hemoglobin parameters of blood such as total hemoglobin (tHb), carboxyhemoglobin (COHb), deoxyhemoglobin (HHb), oxyhemoglobin (O2Hb), methemoglobin (MetHb), and fetal hemoglobin (FHb) as well as total bilirubin (tBil) using optical absorbance.

[0078] FIG. 2 illustrates optical-sample module 20. Optical-sample module 20 includes a light-emitting module 22, a cuvette assembly 40 and a calibrating-light module 60. Light-emitting module 22, as the term implies, emits a visible light beam toward the cuvette assembly 40 that is then received by the calibrating-light module 60, which is then transmitted to spectrometer module 100. The light beam 12 defines an optical path 21.

[0079] FIGS. 3-3A illustrate perspective views of the embodiment of light-emitting module 22 of FIG. 2. Light-emitting module 22 includes a light-emitting module substrate 24 that contains an electrical circuit (not shown) and a light-emitting optics assembly 25. Light-emitting optics assembly 25 has an optics assembly housing 26 with an optics assembly end 26a. A beam of visible light 28a emits from optics assembly end 26a of light-emitting optics assembly 25 when light-emitting module 22 is powered on by a signal received from processor module 150. FIG. 3A illustrates light-emitting optics assembly 25 with optics assembly housing 26 removed exposing a plurality of optical components B contained within light-emitting assembly 25.

[0080] Turning now to FIG. 3B, there is illustrated an enlarged side view of the plurality of optical components B of FIG. 3A. In this embodiment, optical components B includes a light-emitting diode (LED) light source 28, a collimating lens 30, a first diffuser 32, a circular polarizer 34, a focusing lens 36, and an optional protective window 38. Circular polarizer 34 provides a distinct advantage. This advantage provides improved sensitivity and accuracy of the system. Hemoglobin has optical rotary characteristics, which means that the polarization sensitivity of a spectrometer will cause an absorbance error if non-circularly polarized light is used to measure hemoglobin absorbance. Unlike for other polarization states of light, the polarization state of the circularly polarized light is not changed when passing through hemoglobin. Thus, the polarization response of the spectrometer is the same for the circularly polarized light passing through the hemoglobin as it is for the reference scan taken with the cuvette filled with a transparent fluid.

[0081] FIGS. 4 and 5 illustrated front and rear perspective views of one embodiment of the cuvette assembly 40. Cuvette assembly 40 includes a cuvette substrate 41 and a cuvette module 43. Cuvette substrate 41 provides a support for securing the cuvette assembly 40 within the analyte subsystem 10 and includes a cuvette light path opening 42 that is disposed within optical path 21 and is aligned with the light beam emitted from light-emitting module 22. Cuvette module 43 includes a cuvette first portion 44 having a sample receiving recess 45, a sample inlet port 46, a sample outlet port 47, an electronic chip assembly 48, and a first cuvette window 49, and a cuvette second portion 50 having a second cuvette window 52 (shown in FIG. 6 and delineated as outline 53) opposite and aligned with the first cuvette window 49 where the first and second cuvette windows 49, 52 are aligned with and dispersed within optical path 21. Cuvette first portion 44 and cuvette second portion 50 are bonded to each with or without a gasket disposed between cuvette first and second portions 44, 50. Bonding may be achieved using adhesives, ultrasonic techniques, solvent based techniques, etc. When assembled and as shown in FIG. 6, sample receiving recess 45 of cuvette first portion 44 forms a sample receiving chamber 54 with cuvette second portion 50 that fluidly communicates with sample inlet and outlet ports 46, 47. The distance between first and second cuvette windows 49, 52 of sample receiving chamber 54 define a cuvette optical path length, which is accurately measured and stored within electronic chip 48 for later retrieval by processor module 150. A typical optical path length used in this embodiment of the present invention is 0.0035 inches (0.090 mm).

[0082] Turning now to FIG. 7, there is illustrates an enlarged, rear perspective view of cuvette first and second portions 44, 50. As shown, cuvette first portion 44 has sample chamber recess 45 with first cuvette window 49 and electronic chip recess 48a for receiving electronic chip assembly 48. Cuvette second portion 50 has second cuvette window 52 that forms sample receiving chamber 54 when assembled together with cuvette first portion 44. Second cuvette window 52 as delineated by an outline 53 on cuvette second portion 50 is a raised surface that forms a water-tight seal around sample chamber recess 45 and sample receiving chamber 54. Optionally, a thin gasket may be positioned between cuvette first and second portions 44, 50 to more easily ensure a water-tight seal. FIG. 8 shows a rear view of cuvette first portion 44 with electronic chip assembly 48 disposed within electronic chip recess 48a. Electronic chip assembly 48 includes a chip circuit board 48b and an electronic chip 48c that stores the cuvette optical path length value for the particular cuvette module 43. First cuvette window 49 is disposed within the optical path 21 and transmits the light beam passing through the sample to the calibrating light module 60, which then passes the light beam to the spectrometer module 100.

[0083] Turning now to FIG. 9, there is illustrated one embodiment of the calibrating light module 60. Calibrating light module 60 includes a calibrating module housing 62, a light beam receiving portion 64, a calibrating light portion 70, and an optic fiber portion 80 where calibrating module housing 62, light beam receiving portion 64 and optic fiber portion 80 are aligned with optical path 21. Calibrating light portion 70 is spaced from and transverse to optical path 21.

[0084] FIG. 10 is a cross-sectional, elevation view of calibrating light module 60. Calibrating module housing 62 includes a first tubular conduit 62a between a light beam input opening 62b and a light beam exit opening 62c as well as a second tubular conduit 62d that is transverse to and intersects with first tubular conduit 62a on one end and has a calibrating light beam opening 62e on an opposite end.

[0085] Light beam receiving portion 64 houses a collimating lens 66 that collimates light beam 28a received along optical path 21 from cuvette module 43 and directs light beam 28a into first tubular conduit 62a. Disposed within calibrating module housing 62 is beam splitter holder assembly 67 that is disposed transversely across first tubular conduit 62a. Beam splitter holder assembly 67 has an upward slanting surface 67a facing calibrating light beam opening 62e and light beam exit opening 62c within optical path 21. Beam splitter holder assembly 67 supports a second diffuser 68 and a beam splitter 69 (shown in FIG. 11) that is disposed downstream along optical path 21 from second diffuser 68 so that it is positioned to receive calibrating light beam 72a and direct it along optical path 21 and first tubular conduit 62a to light beam exit opening 62c.

[0086] Calibrating light portion 70 includes a calibrating light source 72 disposed adjacent but spaced from optical path 21 that is capable of directing a calibrating light beam 72a into calibrating module housing 62 through a calibrating light opening 62e transversely to optical path 21 toward beam splitter holder assembly 67. Within calibrating light portion 70, there is a collimating lens 74 that collimates calibrating light beam 72a before it is reflected by beam splitter assembly 67 toward light beam exit opening 62c.

[0087] Optic fiber portion 80 is located within optical path 21 at or in the vicinity of light beam exit opening 62c. Optic fiber portion 80 includes a focusing lens 82 and a optic fiber connector assembly 84 that includes a connector housing 86 adapted for receiving an optical fiber assembly 90. Optic fiber portion 80 is adapted to insure that light beam 28a is properly focused by focusing lens 82 into optical fiber assembly 90.

[0088] FIG. 11 is a simplified illustration of FIG. 10 showing the positional relationship of the optical components 66, 68, 69, 74, 82 and light beams 28a, 72a as well as optical fiber assembly 90. As can be seen from FIG. 11, light beam 28a is received by collimating lens 66, transmitted through second diffuser 68 and beam splitter 69 to focusing lens 82 and into optical fiber assembly 90. As previously discussed, the importance of using a pair of diffusers (first diffuser 32 and second diffuser 68) with cuvette module 43 in between the pair of diffusers 32, 68 is that the spatial light distribution will appear the same for the blank scan and the whole blood sample scan. The use of diffusers 32, 68 in this arrangement removes the error effect caused by nonuniformity of the light source and/or variation in the spatial distribution changes of the incident light even if the overall intensity has not changed. Diffusers 32, 68 are chosen so that they diffuse a ray of incident light into the full acceptance cone of the optical component group 120 of the spectrometer module 100. This effectively scrambles the ray completely across the optical measuring field.

[0089] Calibrating light beam 72a when activated is received by collimating lens 74, transmitted to beam splitter 69 and directed to focusing lens 82 where it is focused into optical fiber assembly 90. Calibrating light beam 72a has specific wavelengths of light used for calibrating the wavelength scale of spectrometer module 100. One example of an acceptable calibrating light source 72 is a krypton (Kr) gas discharge lamp, which provides seven Kr line wavelengths in nanometers covering the range of 422 to 695 nm. Prism 131 of light dispersion component 130 has a nonlinear dispersion versus wavelength that requires a polynomial or other function of a higher order. The present invention uses a 5.sup.th order polynomial to the pixel locations of the Kr line peaks to provide residual errors well below the absolute wavelength accuracy requirement of +/−0.03 nm.

[0090] Optical fiber assembly 90 includes an optical fiber 92, a first optical fiber connector 94 and a second optical fiber connector 96 (shown in FIG. 12). First optical fiber connector 94 is secured to a light receiving end 92a of optical fiber 92 and directly and removably connects to connector housing 86 of optic fiber connector assembly 84. One embodiment of optical fiber 92 includes a 200 μm silica core fiber with a numerical aperture (NA) of 0.22.

[0091] Turning now to FIGS. 12 and 13, there is illustrated one embodiment of spectrometer module 100. Spectrometer module 100 includes a spectrometer housing 102, a spectrometer base 104, a spectrometer cover 106 (shown in FIG. 1), an optical fiber housing end 108, and an electrical signal output coupler 103. Spectrometer module 100 has an outside envelope dimension of 11 cm×8 cm×2 cm and optionally includes thermal compensation structures discussed later. Within spectrometer housing 102 are contained the essential components of spectrometer module 100. These components include a light-receiving and converting assembly 110 and an optical component group 120. Optical component group 120 includes an achromatic lens assembly 121 and a light dispersing element 130. Light dispersing element 130 may be a prism 131 or a grating 136. Optical fiber assembly 90 is removably secured to optical fiber housing end 108 at light entrance port 109, which optical fiber assembly 90 transmits the light beams 28a, 72a to spectrometer module 100. As previously mentioned, light beam 28a represents the light transmitted from light-emitting module 22 through cuvette module 43 whereas light beam 72a is the calibrating light transmitted from calibrating light module 60, which is used to calibrate spectrometer module 100.

[0092] Achromatic lens assembly 121 includes a lens mount 122 and a spherical achromatic lens 124. Achromatic lens 124 receives light beams 28a, 72a, as the case may be, and directs the light beam to light dispersion element 130, which in this embodiment is prism 131. Prism 131 has a reflective coating 132 on an outside back surface. Prism 130 refracts light beam 28a and reflects the light back through achromatic lens 124.

[0093] Light-receiving and converting assembly 110 is securely mounted adjacent an inside surface 108a of optical fiber housing end 108. Light-receiving and converting assembly 110 includes a circuit board substrate 112 upon which is mounted a light input slit 114 that is aligned with light-emitting end 92b (not shown) of optical fiber 92. Adjacent input slit 114 is a light-array detector 116 that receives the refracted light from prism 131. Light-array detector 116 converts the refracted light to an electrical signal, which is output through output connector 118 to processor module 150. Providing light input slit 114 and light-array detector 116 adjacent each other on circuit board 112 has several advantages. This feature greatly simplifies the construction and improves the precision of spectrometer module 100. Other spectrometers place these items on separate planes, where they have separate mounting structures, and have to be adjusted independently. This feature of mounting the input slit and light-array detector adjacent each other on circuit board 112 eliminates the need to mount and position each structure (i.e. slit and detector) separately.

[0094] FIG. 14 is an enlarged view of light-receiving and converting assembly 110. Light input slit 114 is 15 μm wide by 1000 μm long that projects an optical fiber-slit image that is a rectangle approximately 15 μm wide by 200 μm high onto the light-array detector 116 (Hamamatsu S10226-10 is an example of a usable light array detector). Input slit 114 is applied directly onto the same circuit board substrate 112 as and in close proximity to light-array detector 116. Light-array detector 116 has a pixel height between about 100 to about 150 μm, which allows a one-to-one imaging of the 200 μm diameter optical fiber onto the detector. In this embodiment, input slit 114 is laser etched in a precise position relative to light-array detector 116 making alignment less labor intensive. Because input slit 114 and light-array detector 116 are only slightly off-axis relative to the center axis of the achromatic lens 124, there is minimal aberration and a one-to-one imaging on light-array detector 116 is possible so that no cylindrical focusing lens is required to shrink the optical fiber image (200 μm diameter fiber) to match the pixel height of light-array detector 116.

[0095] Turning now to FIG. 15, there is a top view of spectrometer module 100 of FIG. 13. Superimposed onto FIG. 15 is a ray trace diagram 140 of the light beam delivered to spectrometer module 100 by optical fiber 92. As shown, light beam 28a enters spectrometer module 100 through input slit 114 toward achromatic lens 124. Achromatic lens 124 is used off-axis; that is, the achromatic lens is slightly off-axis to the light beam 28a. Light beam 28a is transmitted by achromatic lens 124 to prism 131, where light beam 28a is refracted into a plurality of light beams 138a, 138b, 138c of different wavelengths as prisms are ought to do. The plurality of light beams 138a, 138b, 138c are reflected by prism 131 back through achromatic lens 124. Achromatic lens 124 is used off-axis in order to direct the plurality of refracted and reflected light beams 138a, 138b, 138c from prism 131 onto light-array detector 116.

[0096] FIG. 16 is an enlarged view of ray trace diagram 140. Achromatic lens 124 is used off-axis relative to entering light beam 28a. By using achromatic lens 124 off-axis along with prism 131 having a reflective coating 132 on a base of prism 131, there is achieved a compact, simplified, minimal-component spectrometer module 100 capable of being used for measuring hemoglobin parameters and/or total bilirubin parameters in whole blood.

[0097] A change in temperature has a greater effect on beam refraction angle when using a prism instead of a diffraction grating. In the present invention, a thermal-compensating means 160 is provided to compensate for a thermal shift in the incoming light beam caused by the light-dispersing element 130. A temperature change within spectrometer module 100 causes a thermally-induced movement of the slit image from input slit 114 on light-array detector 116 caused in turn by thermally-induced changes in refractive index of the dispersive prism 131. FIG. 16 shows the direction of movement of the image on light-array detector 116 for the thermal refractive index change in prism 131 with arrow 400. If the lens 124 is moved in the opposite direction over the same temperature interval as indicated by arrow 402, the slit image will be moved back to where it should be onto light-array detector 116. To prevent this shift, the thermal-compensating means 160 may be a simple as wrapping spectrometer module 100 with insulation to minimize temperature change within spectrometer module 100 from a temperature change occurring outside of spectrometer module 100 or to place spectrometer module 100 within a temperature controlled space. Another means is to include a temperature controller assembly 170 that includes at least a ribbon heater 172 attached to an inside surface or an outside surface of the spectrometer housing 102 and a temperature sensor 174 such as thermocouple or thermistor to measure the temperature of the spectrometer housing and a heater circuit to maintain a predefined constant temperature. FIGS. 17A and 17B illustrate these possibilities.

[0098] In one embodiment shown in FIG. 17C, achromatic lens mount 122 is a thermal-compensating lens mount. Thermal-compensating lens mount 122 has a fixed mount end 122a and an unfixed mount end 122b. Fixed mount end 122a is fixedly secured to spectrometer base 104 or a baseplate 104a that is securely attached to spectrometer base 104. Unfixed mount end 122b typically has a fastener 126 that extends through a lens mount slot 122c of lens mount 122 and into spectrometer base 104 or baseplate 104a. Between a head 126a of fastener 126 and lens mount 122 is a hold-down spring 128. There is sufficient spacing between lens mount slot 122c and fastener 126 to permit expansion/contraction of lens mount 122 caused by a temperature change. The coefficient of expansion of lens mount 122 is greater than the coefficient of expansion of spectrometer base 104 and/or baseplate 104a so that unfixed mount end 122b permits thermal expansion and contraction of thermal-compensating lens mount 122 in a direction shown by arrow 500, which is linear and transverse to the light beam from input slit 114. This structure allows achromatic lens 124 to slide relative to other components mounted on baseplate 104a and/or spectrometer base 104. Thermal-compensated lens mount 122 ensures that the plurality of light beams 138a, 138b, 138c will always impinge with sufficient intensity onto light-array detector 116 without affecting the electrical signal generated by light-array detector 116 notwithstanding a temperature change within spectrometer housing 102. One such material that meets the requirement that lens mount 122 have a greater coefficient of expansion than spectrometer base 104 and/or baseplate 104a (as the case may be) is a plastic that is a modified polyphenylene ether (PPE) resin consisting of amorphous blends of polyphenylene oxide (PPO) polyphenylene ether (PPE) resin and polystyrene sold under the trademark NORYL®.

[0099] FIG. 18 illustrates an alternative embodiment of lens mount 122. In this embodiment, lens mount 122 has two fixed mount ends 122a, where each end 122a is secured to baseplate 104a and/or spectrometer base 104 by fastener 126. Because both ends 122a of lens mount 122 are fixed, any temperature change within spectrometer module 100 will affect angle of the plurality of light beams 138a, 138b, 138c and where they impinge on light-array detector 116. As previously disclosed regarding the slit image and the length of the light-array detector 116, a temperature change of greater than 0.5° C. will cause the intensity of one of the light beams to not impinge completely on the light-array detector thereby causing an inaccurate reading. To nullify this potential effect, spectrometer module 100 is equipped with a temperature controller assembly (not shown) so that prism 131 and achromatic lens assembly 121 remain at a constant temperature. Although there are several methods available for maintaining the inside of spectrometer module 100 at a constant temperature, one example of such a temperature controller assembly to accomplish this is a ribbon heater with a thermistor (not shown) adhesively attached to the inside or outside of spectrometer module 100, which ribbon heater is controlled by an electronic regulation circuit (not shown). Optionally, spectrometer module 100 may also be insulated either inside or outside or both to more easily maintain a given temperature and protect against changes in temperature in the vicinity surrounding spectrometer module 100. Other mechanisms include placement of spectrometer module 100 within a temperature controlled environment.

[0100] Learning Data:

[0101] A data set of about 180 blood samples from approximately 15 different individuals was developed. The blood samples were manipulated using sodium nitrite to raise MetHb values, and using CO gas to raise COHb values. Plasma was removed from or added to samples to change the tHb level. Bilirubin spiking solution was added to vary the tBil level. A tonometer was used to manipulate the oxygen level. The blood samples were manipulated to cover a large range of analyte values. The blood samples were then measured on a reference lysing pHOx Ultra analyzer equipped with COOx analyzer and analysis software. The whole blood spectra were gathered on a pHOx Ultra analyzer equipped with the high-angle collection optics and other modifications of the present invention, as described earlier, with the lyse supply line completely disconnected and the whole blood samples running directly into the cuvette assembly 40 without lyse or any other dilution. Both analyzers were equipped with Zeonex windows in the respective cuvettes. This data set has been turned into a Matlab cell array file for use with Matlab scripts.

[0102] Prediction Model:

[0103] The next step in the calculation is to create a prediction model. Three models were developed for the analysis: one for the COOx parameters tHb and COHb, a second for HHb and MetHb, and a third for tBil. The quantity for O2Hb was determined by subtracting COHb, HHb, and MetHb from 100%. The X-data array was constructed from terms created from the measured absorbance at the wavelengths between 462-650 nm, 1 nm spacing. The tBil model was developed using the same set of data as the COOx model, except that samples with MetHb values greater than or equal to 20% were left out of the model. For each model, five Y-predictive values were assigned (O2Hb, HHb, COHb, MetHb, tBil) with tHb determined by adding the results for O2Hb, HHb, COHb, and MetHb. The number of Y-orthogonal values needed was determined by manual optimization of the correlation residual of the mapping function blood predictions with the reference analyzer values.

[0104] Using an initial calibration data set, the calibration sequence of a machine learning algorithm establishes a relationship between a matrix of known sample characteristics (the Y matrix) and a matrix of measured absorbance values at several wavelengths and potentially other measured values based on absorbance versus wavelength (the X matrix). Once this relationship is established, it is used by the analyzer to predict the unknown Y values from new measurements of X on whole blood samples.

[0105] Table 1 summarizes the settings and inputs used for the optimized models. The X-data consists of the absorbance and other terms based on absorbance vs. wavelength. In the process of optimizing the model, absorbance derivatives vs. wavelength were added. Models for analytes more sensitive to nonlinear scatter effects were built up with square root terms of the absorbance and its derivative. The model for analytes more affected by scatter had a correction term proportional to the fourth power of the wavelength. The X-vector row has one value for each wavelength for each of the three absorbance-based terms f, g, and h shown in the table for each model.

TABLE-US-00001 TABLE 1 Parameters used to construct algorithm models (KOPLS method). Kernel Y-predictive Y-orthogonal X data structure polynomial Model components components (from absorbance vs. wavelength) exponent tHb, COHb 5 4 [00001]$f\left(\lambda \right)=\sqrt{\frac{\mathrm{dA}\left(\lambda \right)}{d.Math..Math.\lambda }},g\left(\lambda \right)=\frac{\mathrm{dA}\left(\lambda \right)}{d.Math..Math.\lambda },h\left(\lambda \right)=\sqrt{A\left(\lambda \right)}$ 0.5 HHb, MetHb 5 4 [00002]$f\left(\lambda \right)=\frac{\mathrm{dA}\left(\lambda \right)}{d.Math..Math.\lambda },g\left(\lambda \right)=A\left(\lambda \right).Math.{\left(\frac{\lambda }{650.Math..Math.\mathrm{nm}}\right)}^4,h\left(\lambda \right)=A\left(\lambda \right)$ 1.0 tBil 5 16 [00003]$f\left(\lambda \right)=\sqrt{\frac{\mathrm{dA}\left(\lambda \right)}{d.Math..Math.\lambda }},g\left(\lambda \right)=\sqrt{A\left(\lambda \right)},h\left(\lambda \right)=A\left(\lambda \right)$ 1.0

[0106] The calibration set Y matrix is built up as follows from the known values of the calibration sample set of n lysed blood samples:

[00004]$Y=\left[\begin{array}{ccccc}{\mathrm{tHb}}_1& {\mathrm{COHb}}_1& {\mathrm{HHHb}}_1& {\mathrm{MetHb}}_1& {\mathrm{tBil}}_1\\ {\mathrm{tHB}}_2& {\mathrm{COHb}}_2& {\mathrm{HHHb}}_2& {\mathrm{MetHb}}_2& {\mathrm{tBil}}_2\\ \mathrm{.Math.}& \mathrm{.Math.}& \mathrm{.Math.}& \mathrm{.Math.}& \mathrm{.Math.}\\ {\mathrm{tHb}}_n& {\mathrm{COHb}}_n& {\mathrm{HHHb}}_n& {\mathrm{MetHb}}_n& {\mathrm{tBil}}_n\end{array}\right]$

[0107] where tHb is the total hemoglobin value of the lysed blood sample, [0108] COHb is the carboxyhemoblogin value of the lysed blood sample, [0109] HHb is the deoxyhemoglobin value of the lysed blood sample, [0110] MetHb is the methemoglobin value of the lysed blood sample, and [0111] tBil is the total bilirubin value of the lysed blood sample.

[0112] The X matrix is structured as follows:

[00005]$X=\left[\begin{array}{ccc}{f}_1\left({\lambda }_1\right),\mathrm{.Math.}.Math..Math.f_1\left({\lambda }_n\right),& g_1\left({\lambda }_1\right),\mathrm{.Math.}.Math..Math.g_1\left({\lambda }_n\right),& h_1\left({\lambda }_1\right),\mathrm{.Math.}.Math..Math.h_1\left({\lambda }_n\right)\\ \mathrm{.Math.}& \ddots & \mathrm{.Math.}\\ f_n\left({\lambda }_1\right),\mathrm{.Math.}.Math..Math.f_n\left({\lambda }_n\right),& g_n\left({\lambda }_1\right),\mathrm{.Math.}.Math..Math.g_n\left({\lambda }_n\right),& h_n\left({\lambda }_1\right),\mathrm{.Math.}.Math..Math.h_n\left({\lambda }_n\right)\end{array}\right]$

[0113] where: f, g, h are the absorbance-based functions listed in Table 1 versus wavelength, respectively.

[0114] The matrix X includes contributions from absorbance at the various wavelengths. The scope of the invention includes optionally adding other measurements to the calculation to reduce interferent effects.

[0115] Once these matrices are formed, they are used as the calibration set and the mapping function is computed according to the procedures particular to the machine learning algorithm chosen.

[0116] As described previously, conventional partial least squares, linear regression, linear algebra, neural networks, multivariate adaptive regression splines, projection to latent structures, kernel-based orthogonal projection to latent structures, or other machine learning mathematics is used with results obtained from the calibration set of data to determine the empirical relationship (or mapping function) between the absorbance values and the hemoglobin parameters. Typically, a mathematics package is used to generate the results where the package generally has options to select one of the machine learning mathematics known to those skilled in the art. Various mathematics packages exist and include, but are not limited to, Matlab by MatWorks of Natick, Mass., “R” by R Project for Statistical Computing available over the Internet at www.r-project.org, Python from Python Software Foundation and available over the Internet at www.python.org in combination with Orange data mining software from Orange Bioinformatics available over the Internet at orange.biolab.si, to name a few.

[0117] It will be shown that the method of Kernel-Based Orthogonal Projection to Latent Structures (KOPLS) may be used as one type of machine learning algorithm to generate the mapping function. An explanation and description of KOPLS is best exemplified by the following references: Johan Trygg and Svante Wold. “Orthogonal projections to latent structures (O-PLS).” J. Chemometrics 2002; 16: 119-128; Mattias Rantalainen et al. “Kernel-based orthogonal projections to latent structures (K-OPLS).” J. Chemometrics 2007; 21: 376-385; and Max Bylesjö et al. “K-OPLS package: Kernel-based orthogonal projections to latent structures for prediction and interpretation in feature space.” BMC Bioinformatics 2008, 9:106, which references are incorporated herein by reference. The kernel-based mathematics is useful in handling non-linear behavior in systems by using a kernel function to map the original data to a higher order space. Although any of the previously described machine learning mathematics may be used to enable one of ordinary skill in the art to practice the present invention, KOPLS has an additional advantage over other calculations such as, for example, conventional partial least squares because it can not only establish a relationship between quantified variations and analyte values to be determined, but can also remove unquantitated yet consistently present variation in the original data. These unquantitated variations might be due to analyzer and/or blood effects such as scatter losses and other interfering phenomena that are not explicitly measured. By extracting these unquantitated variations from the data, the method leaves behind in the data the information used to predict the measured values.

[0118] Using an initial training data set, the KOPLS model establishes a relationship (mapping function) between the matrix of known sample characteristics (the H matrix), and a matrix of measured absorbance values at several wavelengths and potentially other measured values based on absorbance versus wavelength (the X matrix) as processed through a kernel function as specified by the KOPLS method. Once the KOPLS coefficients of this relationship are established, they are used with the kernel function by the analyzer to predict the unknown hemoglobin parameter values from new measurements of absorbance on samples.

[0119] The kernel function used in this example is a simple linear kernel function described in the Mattias Rantalainen et al. reference listed above and represented by the following equation:

κ(X,X)=<X,X>

where the matrix of measured values X is put into the kernel function and subjected to further processing as specified in the cited KOPLS references above (incorporated by reference) for creating the KOPLS training coefficients.

[0120] Once the set of training coefficients, or mapping function, is established, it is used to predict the hemoglobin parameter values and/or total bilirubin parameter values of a blood sample from future measurements. A single-row X matrix is created from the new measurements, then the value from this single-row X matrix is put through the kernel and mapping functions to produce the hemoglobin parameter values and/or total bilirubin parameter values according to the procedures necessary for the mapping function used according to the KOPLS procedures described in detail in the KOPLS references disclosed previously.

[0121] The data collected from the blood samples described above were put through the KOPLS method in a cross-validation process. Cross-validation is a process for using a data set to test a method. Several data rows are set aside and the rest are used to create a mapping function. The set-aside values are then used as “new” measurements and their Y matrix values calculated. This process is repeated by setting aside other measured values and computing another mapping function. By plotting the known values of the blood data vs. the calculated, the effectiveness of the method may be ascertained by inspecting the plot.

[0122] Turning now to FIGS. 18-23, there are illustrated graphical plots of the correlation results comparing the various hemoglobin parameters of lysed blood to whole blood using the KOPLS method. The blood samples were manipulated to cover a large range of analyte values. The technique of n-fold cross-validation using 60 folds was used to test the data. In this technique, the data set is divided into n=60 separate sets, and the model is made from n−1 of the sets, with the remaining set predicted using the model. The process is repeated 60 times for each group. Every data point is thus predicted using a model made from most of the other data points, without being included in the model.

[0123] FIG. 19 shows the correlation results for tHb using the K-OPLS method. The horizontal axis has units representing the total hemoglobin in grams per deciliter of lysed blood. The vertical axis has units representing total hemoglobin in grams per deciliter of whole blood. As can be seen from the plot, the method of determining tHb of a whole blood sample has a correlation of greater than 99%.

[0124] FIG. 20 shows the correlation results for O2Hb using the K-OPLS method. The horizontal axis has units representing the percent oxyhemoglobin of lysed blood. The vertical axis has unit representing percent oxyhemoglobin of whole blood. As seen from the plot, the method of determining O2Hb of a whole blood sample has a correlation of greater than 99%.

[0125] FIG. 21 shows the correlation results for carboxyhemoglobin using the K-OPLS method. The horizontal axis has units representing the percent carboxyhemoglobin of lysed blood. The vertical axis has unit representing percent carboxyhemoglobin of whole blood. As seen from the plot, the method of determining COHb of a whole blood sample has a correlation of greater than 99%.

[0126] FIG. 22 shows the correlation results for deoxyhemoglobin using the K-OPLS method. The horizontal axis has units representing the percent deoxyhemoglobin of lysed blood. The vertical axis has unit representing percent deoxyhemoglobin of whole blood. As seen from the plot, the method of determining HHb of a whole blood sample has a correlation of greater than 99%.

[0127] FIG. 23 shows the correlation results for methemoglobin using the K-OPLS method. The horizontal axis has units representing the percent methemoglobin of lysed blood. The vertical axis has unit representing percent methemoglobin of whole blood. As seen from the plot, the method of determining MetHb of a whole blood sample has a correlation of greater than 99%.

[0128] FIG. 24 shows the correlation results for tBil using the K-OPLS method. The horizontal axis has units representing the total bilirubin in milligrams per deciliter of lysed blood. The vertical axis has units representing total bilirubin in milligrams per deciliter of whole blood. As can be seen from the plot, the method of determining tBil of a whole blood sample has a correlation of greater than 99%.

[0129] A method of making a whole blood measurement using the COOx analyzer subsystem 10 of the present invention will now be described. An absorbance scan is measured by first recording a transmitted light intensity scan with cuvette module 43 filled with a transparent fluid such as water or analyzer flush solution otherwise known as the ‘blank’ scan. Then a transmitted light intensity scan with cuvette module 43 filled with the whole blood sample is recorded. After corrections for spectrometer dark response and detector linearity, the spectral absorbance is the negative of the logarithm to the base ten of the ratio of the whole blood scan to the transparent fluid scan computed at each wavelength in the measurement range.

[0130] More specifically, a depiction of the components of a COOx analyzer subsystem is shown in FIGS. 1-18. This subsystem embodiment measures the optical absorbance of liquids introduced into cuvette module 43. The light used to perform the absorbance measurement originates from LED light source 28, is collected and transmitted by collimating lens 30, passes through first diffuser 32, circular polarizer 34, focusing lens 36, and optional protective window 38 before reaching cuvette module 43. Critical to an absolute absorbance measurement is knowledge of the cuvette path length. The cuvette path length is pre-measured for each individual cuvette module 43 and programmed into an electronic chip 48c on cuvette module 43. The path length information is read/retrieved by data processor module 130 of the analyzer whenever required.

[0131] After passing through cuvette module 43, the light is collected by lens 66, collimated and sent through second diffuser 68 and beam splitter 69. The purpose of beam splitter 69 is to allow light from calibrating light source 72 (for example, a krypton gas-discharge lamp), collimated by lens 74, to enter optical path 21. Calibrating light source 72 provides light at a few known wavelengths, which are used to periodically recalibrate the wavelength scale of spectrometer module 100. After passing through the beam splitter 69, the light is focused by lens 82 onto an optical fiber 92. The optical fiber 92 guides the light to input slit 114 of spectrometer module 100. The light passes through an achromatic lens 124, goes through light dispersion element 130 with a reflective back 132. The light is wavelength-dispersed by passing through light dispersion element 130 such as, for example, prism 130 then makes a return pass through the lens 124, which re-focuses the light onto the pixels of light-array detector 116. Light-array detector 116 converts the light energy into an electrical signal which represents the spectral intensity of the light. The electrical signal is sent to data processor module 150 for further processing and display of the final results to the user. Light-receiving and converting assembly 110 is a single board that holds input slit 114 and light-array detector 116 in close proximity as an integrated unit.

[0132] Input slit 114 is applied directly onto the same circuit board substrate 112 as and in close proximity to light-array detector 116. Other prior art spectrometers place these components on separate planes where they have separate mounting structures needing independent adjustment and alignment. The mounting scheme of the present invention has several advantages that lower the cost and size of spectrometer module 100: 1) cost of separate mounting structures is avoided, 2) input slit 114 can be laser etched in a precise position relative to light-array detector 116 making alignment less labor intensive, 3) inexpensive spherical surface optics can be used in the optical system since the image of the slit on the detector is only slightly off-axis from the center axis of the optical system, minimizing aberration, and 4) a single alignment procedure for a unified slit and detector assembly replaces alignment procedures for two separate assemblies.

[0133] It is important to note that first diffuser 32 and second diffuser 68 are positioned before and after cuvette module 43, respectively. Optical absorbance measurement of a diffuse sample presents a unique problem. The diffuse transmittance of the sample scrambles the initial spatial light distribution of the measurement system caused by the nonuniformity typical of light sources. Thus, the spatial light distribution of the ‘blank’ scan can be quite different from the whole blood sample scan. Since optical detectors have response that varies spatially, the response can vary due to spatial distribution changes of the incident light, even if the overall intensity has not changed. An absorbance scan which is based on the ratio of the sample scan to the blank scan will have a significant absorbance component due to this effect in addition to the absorbance due to the sample alone. This results in a significant measurement error of the sample absorbance that is intolerable for cooximetry.

[0134] The advantage of placing cuvette module 43 between first and second diffusers 32, 68 is that the spatial light distribution will appear the same for the blank and sample scans, removing this error effect. Diffusers 32, 68 are specially chosen so that they diffuse a ray of incident light into the full acceptance cone of the optical system, but not more so, so that as much light throughput as possible may be preserved while scrambling the light ray completely across the field.

[0135] Although the preferred embodiments of the present invention have been described herein, the above description is merely illustrative. Further modification of the invention herein disclosed will occur to those skilled in the respective arts and all such modifications are deemed to be within the scope of the invention as defined by the appended claims.