Patent Application
20050250217
1. Field of the Invention
This invention relates generally to determining analyte concentrations in material samples.
2. Description of the Related Art
Millions of diabetics draw samples of bodily fluid such as blood on a daily basis to monitor the level of glucose in their bloodstream. A small test strip is often employed to hold the sample for analysis by a suitable analyte detection system. These test strips and detection systems suffer from a variety of problems and also have limited performance.
One embodiment involves a sample element for use in analyzing a concentration of an analyte in a material sample. The sample element comprises a sample chamber having at least one window, and a supply passage extending from the sample chamber. The supply passage defines a supply axis. The sample element further comprises a vent opening in fluid communication with the sample chamber. The vent opening is offset from, the supply axis as the sample element is viewed orthogonal to the window.
Another embodiment involves a sample element for use in analyzing a concentration of an analyte in a material sample. The sample element comprises a sample chamber having at least one generally planar chamber wall, and a supply passage extending from the sample chamber. The supply passage defines a supply axis. The sample element further comprises a vent opening in fluid communication with the sample chamber. The vent opening is offset from the supply axis as the sample element is viewed orthogonal to the chamber wall.
Another embodiment involves a sample element for use in analyzing a concentration of an analyte in a material sample. The sample element comprises a sample chamber, a vent opening in fluid communication with the sample chamber and a vent passage extending from the sample chamber to the vent opening. The vent passage joins the sample chamber at a first end of the vent passage, and the vent passage joins the vent opening at a second end of the vent passage. The vent passage forms at least one bend between the first end and the second end.
Another embodiment involves a sample element for use in analyzing a concentration of an analyte in a material sample. The sample element comprises a sample chamber, and a vent passage extending from the sample chamber to a vent opening. The sample chamber is in fluid communication with the vent opening via the vent passage. The sample element defines a vent axis extending from an intersection of the vent passage with the sample chamber, to the vent opening. The vent passage forms at least one transverse section extending across the vent axis.
Another embodiment involves a sample element for use in analyzing a concentration of an analyte in a material sample. The sample element comprises a first sample chamber having at least one window, a second sample chamber in fluid communication with the first sample chamber, and a supply passage extending from the first sample chamber. The supply passage defines a supply axis. The sample element further comprises a vent opening in fluid communication with the sample chamber. The vent opening is offset from the supply axis as the sample element is viewed orthogonal to the window. The first sample chamber has a first optical pathlength and the second chamber has a second optical pathlength different from the first optical pathlength.
Another embodiment involves a sample element for use in analyzing a concentration of an analyte in a material sample. The sample element comprises a reagentless sample chamber, a vent opening in fluid communication with the sample chamber, and a vent passage extending from the sample chamber to the vent opening. The vent passage joins the sample chamber at a first end of the vent passage. The vent passage joins the vent opening at a second end of the vent passage. The vent passage forms at least one bend between the first end and the second end.
Another embodiment involves a sample element for use in analyzing a concentration of an analyte in a material sample. The sample element comprises a reagentless sample chamber, and a vent passage extending from the sample chamber to a vent opening. The sample chamber is in fluid communication with the vent opening via the vent passage. The sample element defines a vent axis extending from an intersection of the vent passage with the sample chamber, to the vent opening. The vent passage forms at least one transverse section extending across the vent axis.
Certain objects and advantages of the invention are described herein. Of course, it is to be understood that not necessarily all such objects or advantages may be achieved in accordance with any particular embodiment of the invention. Thus, for example, those skilled in the art will recognize that the invention may be embodied or carried out in a manner that achieves or optimizes one advantage or group of advantages as taught herein without necessarily achieving other objects or advantages as may be taught or suggested herein.
All of the embodiments summarized above are intended to be within the scope of the invention herein disclosed. However, despite the foregoing discussion of certain embodiments, only the appended claims (and not the present summary) are intended to define the invention. The summarized embodiments, and other embodiments of the present invention, will become readily apparent to those skilled in the art from the following detailed description of the preferred embodiments having reference to the attached figures, the invention not being limited to any particular embodiment(s) disclosed.
Although certain preferred embodiments and examples are disclosed below, it will be understood by those skilled in the art that the invention extends beyond the specifically disclosed embodiments to other alternative embodiments and/or uses of the invention and obvious modifications and equivalents thereof. Thus it is intended that the scope of the invention herein disclosed should not be limited by the particular disclosed embodiments described below. In any method or process disclosed herein, the acts or operations making up the method/process may be performed in any suitable sequence, and are not necessarily limited to any particular disclosed sequence. For purposes of contrasting various embodiments with the prior art, certain aspects and advantages of these embodiments are described where appropriate herein. Of course, it is to be understood that not necessarily all such aspects or advantages may be achieved in accordance with any particular embodiment. Thus, for example, it should be recognized that the various embodiments may be carried out in a manner that achieves or optimizes one advantage or group of advantages as taught herein without necessarily achieving other aspects or advantages as may be taught or suggested herein.
Section I below discloses various embodiments of an analyte detection system that may be used to detect the concentration of one or more analytes in a material sample. Section II discloses various embodiments of a cuvette or sample element that are suitable for use with the embodiments of the analyte detection system discussed in Section I. The disclosed embodiments of the sample element are configured to support or contain a material sample for analysis by the analyte detection system. In Section III, there are disclosed a number of methods for sample-element referencing, which generally comprises compensating for the effects of the sample element itself on the measurement of analyte concentration. Any one or combination of the methods disclosed in Section III may be executed wholly or partly by appropriate processing hardware in the analyte detection system to support computation of the concentration of the analyte(s) of interest in the sample. Section III also discloses further variations of the analyte detection system and sample element, which are adapted for use in practicing the disclosed methods of sample-element referencing.
Section IV below discusses a number of computational methods or algorithms which may be used to calculate the concentration of the analyte(s) of interest in the sample, and/or to compute or estimate other measures that may be used in support of calculations of analyte concentrations. Any one or combination of the algorithms disclosed in Section IV may be executed by appropriate processing hardware in the analyte detection system to compute the concentration of the analyte(s) of interest in the sample. Section V discusses further embodiments of a sample element having additional, optional features.
The detection system 10 comprises an energy source 20 disposed along a major optical axis, or major axis X, of the system 10. When activated, the energy source 20 generates an energy beam E which advances from the energy source 20 along the major axis X. In one embodiment, the energy source 20 comprises an infrared source and the energy beam E comprises an infrared energy beam.
The energy beam E passes through a filter 25, also situated on the major axis X, before reaching a sample element or cuvette 120, which supports or contains the material sample S. After passing through the sample element 120 and the sample S, the energy beam E reaches a detector 145.
The system 10 thus provides energy beam E that propagates along major optical axis X from energy source 20, through filter 25 and sample element 120, to detector 145. In the embodiment of
With further reference to
In the embodiment shown in
When the energy beam E is filtered with a varying-passband filter, the absorption/transmittance characteristics of the sample S can be analyzed at a number of wavelengths or wavelength bands in a separate, sequential manner. As an example, assume that it is desired to analyze the sample S at four separate wavelengths (Wavelength 1 through Wavelength 4). The varying-passband filter is first operated or tuned to permit the energy beam E to pass at Wavelength 1, while substantially blocking the beam E at most or all other wavelengths to which the detector 145 is sensitive (including Wavelengths 2-4). The absorption/transmittance properties of the sample S are then measured at Wavelength 1, based on the beam E that passes through the sample S and reaches the detector 145. The varying-passband filter is then operated or tuned to permit the energy beam E to pass at Wavelength 2, while substantially blocking other wavelengths as discussed above; the sample S is then analyzed at Wavelength 2 as was done at Wavelength 1. This process is repeated until all of the wavelengths of interest have been employed to analyze the sample S. The collected absorption/transmittance data can then be analyzed by the processor 180 to determine the concentration of the analyte(s) of interest in the material sample S.
By analyzing the sample S at each wavelength or wavelength band in this separate, sequential fashion, greater precision can be attained because the noise, interference, etc. otherwise caused by the detection of wavelengths other than the wavelength of immediate interest, is minimized. However, any other suitable detection methodology may be used with the detection system 10, whether or not the system 10 includes a varying-passband filter.
Although the use of a varying-passband filter offers certain advantages as discussed above, a fixed-passband filter may be used as an alternative filter 25, to permit a selected wavelength or wavelength band to pass through the sample S for analysis thereof.
As used herein, the term “material sample” (or, alternatively, “sample”) is a broad term and is used in its ordinary sense and includes, without limitation, any collection of material which is suitable for analysis by the analyte detection system 10. For example, the material sample S may comprise whole blood, blood components (e.g., plasma or serum), interstitial fluid, intercellular fluid, saliva, urine, sweat and/or other organic or inorganic materials, or derivatives of any of these materials. In one embodiment, whole blood or blood components may be drawn from a patient's capillaries. As used herein, the term “analyte” is a broad term and is used in its ordinary sense and includes, without limitation, any chemical species the presence or concentration of which is sought in the material sample S by the analyte detection system 10. For example, the analyte(s) which may be detected by the analyte detection system 10 include but not are limited to glucose, ethanol, insulin, water, carbon dioxide, blood oxygen, cholesterol, bilirubin, ketones, fatty acids, lipoproteins, albumin, urea, creatinine, white blood cells, red blood cells, hemoglobin, oxygenated hemoglobin, carboxyhemoglobin, organic molecules, inorganic molecules, pharmaceuticals, cytochrome, various proteins and chromophores, microcalcifications, electrolytes, sodium, potassium, chloride, bicarbonate, and hormones.
The detection system 10 shown in
With further reference to
The primary filter 40 is preferably configured to substantially maintain its operating characteristics (center wavelength, passband width) where some or all of the energy beam E deviates from normal incidence by a cone angle of up to about twelve degrees relative to the major axis X. In further embodiments, this cone angle may be up to about 15 degrees or 20 degrees, or up to about 15 to 35 degrees. The primary filter 40 may be said to “substantially maintain” its operating characteristics where any changes therein are insufficient to affect the performance or operation of the detection system 10 in a manner that would raise significant concerns for the user(s) of the system in the context in which the system 10 is employed.
In the embodiment illustrated in
In alternative arrangements, the single primary filter 40 depicted in
The filter wheel 50, in the embodiment depicted in
In one embodiment, the wheel body 52 can be formed from molded plastic, with each of the secondary filters 60 having a 5 mm×5 mm square configuration and a thickness of 1 mm. Each of the filters 60, in this embodiment of the wheel body, is axially aligned with a circular aperture of 4 mm diameter, and the aperture centers define a circle of about 1.70 inches diameter, which circle is concentric with the wheel body 52. The body 52 itself is circular, with an outside diameter of 2.00 inches.
Each of the secondary filter(s) 60 is preferably configured to operate as a narrow band filter, allowing only a selected energy wavelength or wavelength band (i.e., a filtered energy, beam (Ef) to pass therethrough. As the filter wheel 50 rotates about its rotational center RC, each of the secondary filter(s) 60 is, in turn, disposed along the major axis X for a selected dwell time corresponding to each of the secondary filter(s) 60.
The “dwell time” for a given secondary filter 60 is the time interval, in an individual measurement run of the system 10, during which both of the following conditions are true: (i) the filter is disposed on the major axis X; and (ii) the source 20 is energized. The dwell time for a given filter may be greater than or equal to the time during which the filter is disposed on the major axis X during an individual measurement run. In one embodiment of the analyte detection system 10, the dwell time corresponding to each of the secondary filter(s) 60 is less than about 1 second. However, the secondary filter(s) 60 can have other dwell times, and each of the filter(s) 60 may have a different dwell time during a given measurement run.
Referring again to
From the secondary filter 60, the filtered energy beam (Ef) passes through a beam splitter 100 disposed along the major axis X and having a face 100a disposed at an included angle θ relative to the major axis X. The splitter 100 preferably separates the filtered energy beam (Ef) into a sample beam (Es) and a reference beam (Er).
With further reference to
At least a fraction of the sample beam (Es) is transmitted through the sample S and continues onto a second lens 140 disposed along the major axis X. The second lens 140 is configured to focus the sample beam (Es) onto a sample detector 150, thus increasing the flux density of the sample beam (Es) incident upon the sample detector 150. The sample detector 150 is configured to generate a signal corresponding to the detected sample beam (Es) and to pass the signal to a processor 180, as discussed in more detail below.
The reference beam (Er) is directed from the beam splitter 100 to a third lens 160 disposed along a minor axis Y generally orthogonal to the major axis X. The third lens 160 is configured to focus the reference beam (Er) onto a reference detector 170, thus increasing the flux density of the reference beam (Er) incident upon the reference detector 170. In one embodiment, the lenses 110, 140, 160 may be formed from a material which is highly transmissive of infrared radiation, for example germanium or silicon. In addition, any of the lenses 110, 140 and 160 may be implemented as a system of lenses, depending on the desired optical performance. The reference detector 170 is also configured to generate a signal corresponding to the detected reference beam (Er) and to pass the signal to the processor 180, as discussed in more detail below. Except as noted below, the sample and reference detectors 150, 170 may be generally similar to the detector 145 illustrated in
In further variations of the detection system 10 depicted in
The energy source 20 of the embodiment of
The energy source 20 is preferably configured to selectably operate at a modulation frequency between about 1 Hz and 30 Hz and have a peak operating temperature of between about 1070 degrees Kelvin and 1170 degrees Kelvin. Additionally, the source 20 preferably operates with a modulation depth greater than about 80% at all modulation frequencies. The energy source 20 preferably emits electromagnetic radiation in any of a number of spectral ranges, e.g., within infrared wavelengths; in the mid-infrared wavelengths; above about 0.8 μm; between about 5.0 μm and about 20.0 μm; and/or between about 5.25 μm and about 12.0 μm. However, in other embodiments, the detection system 10 may employ an energy source 20 which is unmodulated and/or which emits in wavelengths found anywhere from the visible spectrum through the microwave spectrum, for example anywhere from about 0.4 μm to greater than about 100 μm. In still other embodiments, the energy source 20 can emit electromagnetic radiation in wavelengths between about 3.5 μm and about 14 μm, or between about 0.8 μm and about 2.5 μm, or between about 2.5 μm and 20 μm, or between about 20 μm and about 100 μm, or between about 6.85 μm and about 10.10 μm. In yet other embodiments, the energy source 20 can emit electromagnetic radiation within the radio frequency (RF) range or the terahertz range. All of the above-recited operating characteristics are merely exemplary, and the source 20 may have any operating characteristics suitable for use with the analyte detection system 10.
A power supply (not shown) for the energy source 20 is preferably configured to selectably operate with a duty cycle of between about 30% and about 70%. Additionally, the power supply is preferably configured to selectably operate at a modulation frequency of about 10 Hz, or between about 1 Hz and about 30 Hz. The operation of the power supply can be in the form of a square wave, a sine wave, or any other waveform defined by a user.
With further reference to
As illustrated in
The inner surfaces 32 of the collimator 30 cause the rays making up the energy beam E to straighten (i.e., propagate at angles increasingly parallel to the major axis X) as the beam E advances downstream, so that the energy beam E becomes increasingly or substantially cylindrical and oriented substantially parallel to the major axis X. Accordingly, the inner surfaces 32 are highly reflective and minimally absorptive in the wavelengths of interest, such as infrared wavelengths.
The tube 30a itself may be fabricated from a rigid material such as aluminum, steel, or any other suitable material, as long as the inner surfaces 32 are coated or otherwise treated to be highly reflective in the wavelengths of interest. For example, a polished gold coating may be employed. Preferably, the inner surface(s) 32 of the collimator 30 define a circular cross-section when viewed orthogonal to the major axis X; however, other cross-sectional shapes, such as a square or other polygonal shapes, parabolic or elliptical shapes may be employed in alternative embodiments.
As noted above, the filter wheel 50 shown in
In another embodiment, the filter wheel 50 comprises twenty secondary filters 60, each of which is configured to allow a filtered energy beam (Ef) to travel therethrough with a nominal center wavelengths of: 4.275 μm, 4.5 μm, 4.7 μm, 5.0 μm, 5.3 μm, 6.056 μm, 7.15 μm, 7.3 μm, 7.55 μm, 7.67 μm, 8.06 μm, 8.4 μm, 8.56 μm, 8.87 μm, 9.15 μm, 9.27 μm, 9.48 μm, 9.68 μm, 9.82 μm, and 10.06 μm. (This set of wavelengths may also be employed with or in any of the embodiments of the analyte detection system 10 disclosed herein.) In still another embodiment, the secondary filters 60 may conform to any one or combination of the following specifications: center wavelength tolerance of ±0.01 μm, half-power bandwidth tolerance of ±0.01 μm; peak transmission greater than or equal to 75%; cut-on/cut-off slope less than 2%; center-wavelength temperature coefficient less than 0.01% per degree Celsius; out of band attenuation greater than OD 5 from 3 μm to 12 μm; flatness less than 1.0 waves at 0.6328 μm; surface quality of E-E per Mil-F-48616; and overall thickness of about 1 mm.
In still another embodiment, the secondary filters mentioned above may conform to any one or combination of the following half-power bandwidth (“HPBW”) specifications:
In still further embodiments; the secondary filters may have a center wavelength tolerance of ±0.5% and a half-power bandwidth tolerance of ±0.02 μm.
Of course, the number of secondary filters employed, and the center wavelengths and other characteristics thereof, may vary in further embodiments of the system 10, whether such further embodiments are employed to detect glucose, or other analytes instead of or in addition to glucose. For example, in another embodiment, the filter wheel 50 can have fewer than fifty secondary filters 60. In still another embodiment, the filter wheel 50 can have fewer than twenty secondary filters 60. In yet another embodiment, the filter wheel 50 can have fewer than ten secondary filters 60.
In one embodiment, the secondary filters 60 each measure about 10 mm long by 10 mm wide in a plane orthogonal to the major axis X, with a thickness of about 1 mm. However, the secondary filters 60 can have any other (e.g., smaller) dimensions suitable for operation of the analyte detection system 10. Additionally, the secondary filters 60 are preferably configured to operate at a temperature of between about 5° C. and about 35° C. and to allow transmission of more than about 75% of the energy beam E therethrough in the wavelength(s) which the filter is configured to pass.
According to the embodiment illustrated in
A reflector tube 98 is preferably positioned to receive the filtered energy beam (Ef) as it advances from the secondary filter(s) 60. The reflector tube 98 is preferably secured with respect to the secondary filter(s) 60 to substantially prevent introduction of stray electromagnetic radiation, such as stray light, into the reflector tube 98 from outside of the detection system 10. The inner surfaces of the reflector tube 98 are highly reflective in the relevant wavelengths and preferably have a cylindrical shape with a generally circular cross-section orthogonal to the major and/or minor axis X, Y. However, the inner surface of the tube 98 can have a cross-section of any suitable shape, such as oval, square, rectangular, etc. Like the collimator 30, the reflector tube 98 may be formed from a rigid material such as aluminum, steel, etc., as long as the inner surfaces are coated or otherwise treated to be highly reflective in the wavelengths of interest. For example, a polished gold coating may be employed.
According to the embodiment illustrated in
The major section 98a conducts the filtered energy beam (Ef) from the first end 98c to the beam splitter 100, which is housed in the major section 98a at the intersection of the major and minor axes X, Y. The major section 98a also conducts the sample beam (Es) from the beam splitter 100, through the first lens 110 and to the second end 98d. From the second end 98d the sample beam (Es) proceeds through the sample element 120, holder 130 and second lens 140, and to the sample detector 150. Similarly, the minor section 98b conducts the reference beam (Er) from the beam splitter 100, through the third lens 160 and to the third end 98e. From the third end 98e the reference beam (Er) proceeds to the reference detector 170.
The sample beam (Es) preferably comprises from about 75% to about 85% of the energy of the filtered energy beam (Ef). More preferably, the sample beam (Es) comprises about 80% of the energy of the filtered energy beam (Es). The reference beam (Er) preferably comprises from about 15% and about 25% of the energy of the filtered energy beam (Es). More preferably, the reference beam (Er) comprises about 20% of the energy of the filtered energy beam (Ef). Of course, the sample and reference beams may take on any suitable proportions of the energy beam E.
The reflector tube 98 also houses the first lens 110 and the third lens 160. As illustrated in
The sample element 120 is retained within the holder 130, which is preferably oriented along a plane generally orthogonal to the major axis X. The holder 130 is configured to be slidably displaced between a loading position and a measurement position within the analyte detection system 10. In the measurement position, the holder 130 contacts a stop edge 136 which is located to orient the sample element 120 and the sample S contained therein on the major axis X.
The structural details of the holder 130 depicted in
As with the embodiment depicted in
The receiving portion 152a houses the second lens 140 in the lens chamber 152d proximal to the aperture 152c. The sample detector 150 is also disposed in the lens chamber 152d downstream of the second lens 140 such that a detection plane 154 of the detector 150 is substantially orthogonal to the major axis X. The second lens 140 is positioned such that a plane 142 of the lens 140 is substantially orthogonal to the major axis X. The second lens 140 is configured, and is preferably disposed relative to the holder 130 and the sample detector 150, to focus substantially all of the sample beam (Es) onto the detection plane 154, thereby increasing the flux density of the sample beam (Es) incident upon the detection plane 154.
With further reference to
The receiving portion 152a preferably also houses a printed circuit board 158 disposed between the gasket 157 and the sample detector 150. The board 158 connects to the sample detector 150 through at least one connecting member 150a. The sample detector 150 is configured to generate a detection signal corresponding to the sample beam (Es) incident on the detection plane 154. The sample detector 150 communicates the detection signal to the circuit board 158 through the connecting member 150a, and the board 158 transmits the detection signal to the processor 180.
In one embodiment, the sample detector 150 comprises a generally cylindrical housing 150a, e.g. a type TO-39 “metal can” package, which defines a generally circular housing aperture 150b at its “upstream” end. In one embodiment, the housing 150a has a diameter of about 0.323 inches and a depth of about 0.248 inches, and the aperture 150b may have a diameter of about 0.197 inches.
A detector window 150c is disposed adjacent the aperture 150b, with its upstream surface preferably about 0.078 inches (+/−0.004 inches) from the detection plane 154. (The detection plane 154 is located about 0.088 inches (+/−0.004 inches) from the upstream edge of the housing 150a, where the housing has a thickness of about 0.010 inches.) The detector window 150c is preferably transmissive of infrared energy in at least a 3-12 micron passband; accordingly, one suitable material for the window 150c is germanium. The endpoints of the passband may be “spread” further to less than 2.5 microns, and/or greater than 12.5 microns, to avoid unnecessary absorbance in the wavelengths of interest. Preferably, the transmittance of the detector window 150c does not vary by more than 2% across its passband. The window 150c is preferably about 0.020 inches in thickness. The sample detector 150 preferably substantially retains its operating characteristics across a temperature range of −20 to +60 degrees Celsius.
The receiving portion 172a houses the reference detector 170 in the chamber 172d proximal to the aperture 172c. The reference detector 170 is disposed in the chamber 172d such that a detection plane 174 of the reference detector 170 is substantially orthogonal to the minor axis Y. The third lens 160 is configured to substantially focus the reference beam (Er) so that substantially the entire reference beam (Er) impinges onto the detection plane 174, thus increasing the flux density of the reference beam (Er) incident upon the detection plane 174.
With further reference to
The receiving portion 172a preferably also houses a printed circuit board 178 disposed between the gasket 177 and the reference detector 170. The board 178 connects to the reference detector 170 through at least one connecting member 170a. The reference detector 170 is configured to generate a detection signal corresponding to the reference beam (Er) incident on the detection plane 174. The reference detector 170 communicates the detection signal to the circuit board 178 through the connecting member 170a, and the board 178 transmits the detection signal to the processor 180.
In one embodiment, the construction of the reference detector 170 is generally similar to that described above with regard to the sample detector 150.
In one embodiment, the sample and reference detectors 150, 170 are both configured to detect electromagnetic radiation in a spectral wavelength range of between about 0.8 μm and about 25 μm. However, any suitable subset of the foregoing set of wavelengths can be selected. In another embodiment, the detectors 150, 170 are configured to detect electromagnetic radiation in the wavelength range of between about 4 μm and about 12 μm. The detection planes 154, 174 of the detectors 150, 170 may each define an active area about 2 mm by 2 mm or from about 1 mm by 1 mm to about 5 mm by 5 mm; of course, any other suitable dimensions and proportions may be employed. Additionally, the detectors 150, 170 may be configured to detect electromagnetic radiation directed thereto within a cone angle of about 45 degrees from the major axis X.
In one embodiment, the sample and reference detector subsystems 150, 170 may further comprise a system (not shown) for regulating the temperature of the detectors. Such a temperature-regulation system may comprise a suitable electrical heat source, thermistor, and a proportional-plus-integral-plus-derivative (PID) control. These components may be used to regulate the temperature of the detectors 150, 170 at about 35° C. The detectors 150, 170 can also optionally be operated at other desired temperatures. Additionally, the PID control preferably has a control rate of about 60 Hz and, along with the heat source and thermistor, maintains the temperature of the detectors 150, 170 within about 0.1 IC of the desired temperature.
The detectors 150, 170 can operate in either a voltage mode or a current mode, wherein either mode of operation preferably includes the use of a pre-amp module. Suitable voltage mode detectors for use with the analyte detection system 10 disclosed herein include: models LIE 302 and 312 by InfraTec of Dresden, Germany; model L2002 by BAE Systems of Rockville, Md.; and model LTS-1 by Dias of Dresden, Germany. Suitable current mode detectors include: InfraTec models LIE 301, 315, 345 and 355; and 2×2 current-mode detectors available from Dias.
In one embodiment, one or both of the detectors 150, 170 may meet the following specifications, when assuming an incident radiation intensity of about 9.26×10−4 watts (rms) per cm2, at 10 Hz modulation and within a cone angle of about 15 degrees: detector area of 0.040 cm2 (2 mm×2 mm square); detector input of 3.70×10−5 watts (rms) at 10 Hz; detector sensitivity of 360 volts per watt at 10 Hz; detector output of 1.333×10−2 volts (rms) at 10 Hz; noise of 8.00×10−8 volts/sqrtHz at 10 Hz; and signal-to-noise ratios of 1.67×105 rms/sqrtHz and 104.4 dB/sqrtHz; and detectivity of 1.00×109 cm sqrtHz/watt.
In alternative embodiments, the detectors 150, 170 may comprise microphones and/or other sensors suitable for operation of the detection system 10 in a photoacoustic mode.
Any of the disclosed embodiments of the analyte detection system 10 may comprise a near-patient testing system. As used herein, “near-patient testing system” is used in its ordinary sense and includes, without limitation, test systems that are configured to be used where the patient is rather than exclusively in a laboratory, e.g., systems that can be used at a patient's home, in a clinic, in a hospital, or even in a mobile environment. Users of near-patient testing systems can include patients, family members of patients, clinicians, nurses, or doctors. A “near-patient testing system” could also include a “point-of-care” system.
The components of any of the embodiments of the analyte detection system 10 may be partially or completely contained in an enclosure or casing (not shown) to prevent stray electromagnetic radiation, such as stray light, from contaminating the energy beam E. Any suitable casing may be used. Similarly, the components of the detection system 10 may be mounted on any suitable frame or chassis (not shown) to maintain their operative alignment as depicted in
Any of the disclosed embodiments of the analyte detection system 10 may in one embodiment be configured to be operated easily by the patient or user. As such, the system 10 is may comprise a portable device. As used herein, “portable” is used in its ordinary sense and means, without limitation, that the system 10 can be easily transported by the patient and used where convenient. For example, the system 10 is advantageously small. In one preferred embodiment, the system 10 is small enough to fit into a purse or backpack. In another embodiment, the system 10 is small enough to fit into a pants pocket. In still another embodiment, the system 10 is small enough to be held in the palm of a hand of the user.
When enclosed in the external casing (not shown), the analyte detection system 10 is advantageously no larger than 5.4 inches long by 3.5 inches wide by 1.5 inches deep. In further embodiments, the enclosed system 10 may be no more than about 80% or 90% of this size. In still further embodiments, the enclosed analyte detection system 10 takes up less than about one-half, or less than about one-tenth the volume of a laboratory-grade Fourier Transform Infrared Spectrometer (FTIR), which typically measures about 2 feet wide by one foot high by one foot deep. Accordingly, in these embodiments the enclosed analyte detection system 10 has a volume of less than about 1750 cubic inches, or less than about 350 cubic inches. In still another embodiment, the analyte detection system 10 measures about 3.5 inches by 2.5 inches by 2.0 inches, and/or has a volume of about 10 cubic inches. Despite its relatively small size as disclosed above, the analyte detection system 10 achieves very good performance in a variety of measures. However, the analyte detection system 10 is not limited to these sizes and can be manufactured to other dimensions.
In one method of operation, the analyte detection system 10 shown in
For each secondary filter 60 selectively aligned with the major axis X, the sample detector 150 detects the portion of the sample beam (Es), at the wavelength or wavelength band corresponding to the secondary filter 60, that is transmitted through the material sample S. The sample detector 150 generates a detection signal corresponding to the detected electromagnetic radiation and passes the signal to the processor 180. Simultaneously, the reference detector 170 detects the reference beam (Er) transmitted at the wavelength or wavelength band corresponding to the secondary filter 60. The reference detector 170 generates a detection signal corresponding to the detected electromagnetic radiation and passes the signal to the processor 180. Based on the signals passed to it by the detectors 150, 170, the processor 180 computes the concentration of the analyte(s) of interest in the sample S, and/or the absorbance/transmittance characteristics of the sample S at one or more wavelengths or wavelength bands employed to analyze the sample. The processor 180 computes the concentration(s), absorbance(s), transmittance(s), etc. by executing a data processing algorithm or program instructions residing within the memory 185 accessible by the processor 180.
The signal generated by the reference detector may be used to monitor fluctuations in the intensity of the energy beam emitted by the source 20, which fluctuations often arise due to drift effects, aging, wear or other imperfections in the source itself. This enables the processor 180 to identify changes in intensity of the sample beam (Es) that are attributable to changes in the emission intensity of the source 20, and not to the composition of the sample S. By so doing, a potential source of error in computations of concentration, absorbance, etc. is minimized or eliminated.
In one embodiment, the detection system 10 computes an analyte concentration reading by first measuring the electromagnetic radiation detected by the detectors 150, 170 at each center wavelength, or wavelength band, without the sample element 120 present on the major axis X (this is known as an “air” reading). Second, the system 10 measures the electromagnetic radiation detected by the detectors 150, 170 for each center wavelength, or wavelength band, with the sample element 120 present on the major axis X, but without the material sample S (i.e., a “dry” reading). Third, the system 10 measures the electromagnetic radiation detected by the detectors 150, 170 with an opaque element or mask (such as a secondary filter 60 which is substantially opaque in the wavelength(s) of interest) disposed on the major axis X between the source 20 and beam splitter 100, and/or with the source 20 switched off (i.e., a “dark” reading). Fourth, the system 10 measures the electromagnetic radiation detected by the detectors 150, 170 for each center wavelength, or wavelength band, with the material sample S present in the sample element 120, and the sample element 120 and sample S in position on the major axis X (i.e., a “wet” reading). Finally, the processor 10 computes the concentration(s), absorbance(s) and/or transmittances relating to the sample S based on these compiled readings.
In an operational block 190a, a “dark” reading is taken as discussed above, wherein the processor 180 computes a dark transmittance reading TD, which is stored in memory. Next, an “air” reading is taken, as discussed above, in an operational block 190b. This operation may comprise computing and storing an air transmittance reading TA, and a gain factor GF which equals 100%/TA (see operational block 190c), as well as a simultaneous air reference intensity RIA (operational block 190d), based on the output of the reference detector 170 during the air reading. In one embodiment, any or all of the air transmittance reading TA, gain factor GF and air reference intensity RIA are computed at each of the wavelengths or wavelength bands of interest, yielding, for example, TAλ1, TAλ2, . . . TAλn; GFλ1, GFλ2, . . . GFλn; etc.
In operational block 190e, a “wet” reading is taken as described above, with the sample element and sample S therein positioned on the major axis X. The wet reading yields a series of wavelength-specific transmittance values Tλ1, Tλ2, . . . Tλn in each of the wavelengths or bands of interest, which values are stored in memory, along with simultaneously-recorded corresponding wet reference intensities RIWλ1, RIWλ2, . . . RIWλN which arise from the output of the reference detector 170 at each wavelength/band of interest while the wet reading is taken. The wet reading is then shifted (see block 190f) by subtracting the dark transmittance reading(s) from each of the wavelength-specific transmittance values Tλ1, Tλ2, . . . Tλn, yielding shifted transmittance values TSλ1, TSλ2, . . . TSλn. In block 190g, the shifted transmittance values are scaled by multiplying each of the values TSλ1, TSλ2, . . . TSλn, by the previously-computed gain factor (s) GF. Where wavelength-specific gain factors GFλ1, GFλ2, . . . GFλn, have been computed, each shifted transmittance value TSλi is multiplied by its corresponding gain factor GFλi. Either option yields shifted, scaled transmittance values TSSλ1, TSSλ2, . . . TSSλn.
In operational block 190h, each of the shifted, scaled transmittance values TSSλ1, TSSλ2, . . . TSSλn is source-referenced. First, a series of reference factors RFλ1, RFλ2, . . . RFλn are computed by dividing the air reference intensity RIA by each of the wet reference intensities RIWλ1, RIWλ2, . . . RIWλn. Where a series of air reference intensities RIAλ1, RIAλ2, . . . RIAλn, have been compiled, each air reference intensity RIAλi is divided by its corresponding wet reference intensity RIWλi to generate the reference factors RFλ1, RFλ2, . . . RFλn. Each of the shifted, scaled transmittance values TSSλ1, TSSλ2, . . . TSSλn, is source-referenced by multiplying it by the corresponding reference factor RFλ1, RFλ2, . . . RFλn to generate shifted, scaled, source-referenced transmittance values TSSRλ1, TSSRλ2, . . . TSSRλn.
Each of the shifted, scaled, source-referenced transmittance values TSSRλ1, TSSRλ2, . . . TSSRλn, is sample-element referenced in operational block 190i, to yield final transmittance values TFλ1, TFλ2, . . . TFλn. Any of the sample-element referencing methods disclosed herein may be employed. While the sample-element referencing operation 190i is depicted at the end of the illustrated method 190, this referencing 190i may in practice comprise a number of sub-operations that are intermingled with the other operations of the method 190, as will become apparent from the discussion herein of the various sample-element referencing methods. Regardless of the nature of the sample-element referencing operation, the final transmittance values TFλ1, TFλ2, . . . TFλn may then be employed to compute the concentration of the analyte(s) of interest in the sample S.
In further embodiments, any suitable variation of the method 190 may be employed. Any one or combination of the operations 190a-190i may be omitted, depending on the desired level of measurement precision. For example, the dark reading 190a and subsequent shift 190f may be omitted. Instead of or in addition to omission of these operations 190a, 190f, the air reading 190b may be omitted, in whole or in part. Where measurement/computation of the air transmittance reading TA and gain factor GF (block 190c) are omitted, the scaling operation 190g may also be omitted; likewise, where measurement/computation of the air reference intensity RIA (block 190d) is omitted, the source referencing operation 190h may also be omitted. Finally, instead or in addition to the foregoing omissions, the sample element referencing operation 190i may be omitted.
In any variation of the method 190, the operations may be performed in any suitable sequence, and the method 190 is by no means limited to the sequence depicted in
In still further embodiments, any of the computational algorithms or methods discussed below may be employed to compute the concentration of the analyte(s) of interest in the sample S from (any) final transmittance values TFλ1, TFλ2, . . . TFλn output by any of the embodiments of the method 190 discussed herein. Any of the disclosed embodiments of the method 190 may reside as program instructions in the memory 185 so as to be accessible for execution by the processor 180 of the analyte detection system 10.
In one embodiment, the processor 180 is configured to communicate the analyte concentration results and/or other information to a display controller (not shown), which operates a display (not shown), such as an LCD display, to present the information to the user. In one embodiment, the processor 180 can communicate to the display controller only the concentration of glucose in the material sample S. In another embodiment, the processor 180 can communicate to the display controller the concentration of ketone in addition to the concentration of glucose in the material sample S. In still another embodiment, the processor 180 can communicate to the display controller the concentration of multiple analytes in the material sample S. In yet another embodiment, the display outputs the glucose concentration with a resolution of 1 mg/dL.
Additional capabilities of various embodiments of the analyte detection system 10, and other related information, may be found in U.S. Patent Application Publication No. U.S. 2005/0038674A1, published Feb. 17, 2005, titled SYSTEM AND METHOD FOR MANAGING A CHRONIC MEDICAL CONDITION. The entire contents of this publication are hereby incorporated by reference herein and made a part of this specification.
In view of the foregoing disclosure of certain embodiments of the analyte detection system 10, the following section discusses various embodiments of a cuvette or sample element for use with the analyte detection system 10. As used herein, “sample element” is a broad term and is used in its ordinary sense and includes, without limitation, structures that have a sample chamber and at least one sample chamber wall, but more generally includes any of a number of structures that can hold, support or contain a material sample and that allow electromagnetic radiation to pass through a sample held, supported or contained thereby; e.g., a cuvette, test strip, etc.
In the embodiment illustrated in
In various embodiments, the material that makes up the window(s) of the sample element 120 is completely transmissive, i.e., it does not absorb any of the electromagnetic radiation from the source 20 and first and second filters 40, 60 that is incident upon it. In another embodiment, the material of the window(s) has some absorption in the electromagnetic range of interest, but its absorption is negligible. In yet another embodiment, the absorption of the material of the window(s) is not negligible, but it is stable for a relatively long period of time. In another embodiment, the absorption of the window(s) is stable for only a relatively short period of time, but the analyte detection system 10 is configured to observe the absorption of the material and eliminate it from the analyte measurement before the material properties can change measurably. Materials suitable for forming the window(s) of the sample element 120 include barium fluoride, silicon, polypropylene, polyethylene, or any polymer with suitable transmissivity (i.e., transmittance per unit thickness) in the relevant wavelength(s). Where the window(s) are formed from a polymer, the selected polymer can be isotactic, atactic or syndiotactic in structure, so as to enhance the flow of the sample between the window(s). One type of polyethylene suitable for constructing the sample element 120 is type 220, as extruded, available from KUBE Ltd. of Staefa, Switzerland.
In one embodiment, the sample element 120 is configured to allow sufficient transmission of electromagnetic energy having a wavelength of between about 4 μm and about 10.5 μm through the window(s) thereof. However, the sample element 120 can be configured to allow transmission of wavelengths in any spectral range emitted by the energy source 20. In another embodiment, the sample element 120 is configured to receive an optical power of more than about 1.0 MW/cm2 from the sample beam (Es) incident thereon for any electromagnetic radiation wavelength transmitted through the secondary filter(s) 60. In still another embodiment, the sample element 120 is configured to allow transmission of about 75% of the electromagnetic energy incident upon the sample chamber 200 therethrough. Preferably, the sample chamber 200 of the sample element 120 is configured to allow a sample beam (Es) advancing toward the material sample S within a cone angle of 45 degrees from the major axis X (see
In the embodiment illustrated in
In operation, the supply opening 206 of the sample element 120 is placed in contact with the material sample S, such as a fluid flowing from a wound on a patient. The fluid is then transported through the sample supply passage 204 and into the sample chamber 200 via capillary action. The vent passage 208 and vent opening 210 improve the sample transport by preventing the buildup of air pressure within the sample element and allowing the sample to displace the air as the sample flows to the sample chamber 200.
Where the upper and lower chamber walls 202c, 202d comprise windows, the distance T (measured along an axis substantially orthogonal to the sample chamber 200 and/or windows 202a, 202b, or, alternatively, measured along an axis of an energy beam (such as but not limited to the energy beam E discussed above) passed through the sample chamber 200) between them comprises an optical pathlength (see
In one embodiment, the transverse size of the sample chamber 200 (i.e., the size defined by the lateral chamber walls 202a, 202b) is about equal to the size of the active surface of the sample detector 150. Accordingly, in a further embodiment the sample chamber 200 is round with a diameter of about 4 mm.
The sample element 120 shown in
The sample element 120 is preferably sized to receive a material sample S having a volume less than or equal to about 3 μL (or less than or equal to about 2 μL, or less than or equal to about 1 μL) and more preferably a material sample S having a volume less than or equal to about 0.85 μL. Of course, the volume of the sample element 120, the volume of the sample chamber 200, etc. can vary, depending on many variables, such as the size and sensitivity of the sample detector 150, the intensity of the radiation emitted by the energy source 20, the expected flow properties of the sample, and whether flow enhancers are incorporated into the sample element 120. The transport of fluid to the sample chamber 200 is achieved preferably through capillary action, but may also be achieved through wicking or vacuum action, or a combination of wicking, capillary action, and/or vacuum action.
With further reference to
The sample chamber 200 preferably comprises a reagentless chamber. In other words, the internal volume of the sample chamber 200 and/or the wall(s) 202 defining the chamber 200 are preferably inert with respect to the sample to be drawn into the chamber for analysis. As used herein, “inert” is a broad term and is used in its ordinary sense and includes, without limitation, substances which will not react with the sample in a manner which will significantly affect any measurement made of the concentration of analyte(s) in the sample with the analyte detection system 10 or any other suitable system, for a sufficient time (e.g., about 1-30 minutes) following entry of the sample into the chamber 200, to permit measurement of the concentration of such analyte(s). Alternatively, the sample chamber 200 may contain one or more reagents to facilitate use of the sample element in sample assay techniques which involve reaction of the sample with a reagent.
In one embodiment, the sample element may be configured to separate plasma from a whole-blood or other similar sample, via employment of an appropriate filter or membrane, between the entry point of the sample into the sample element, and the sample chamber(s). In a sample element so configured, the plasma flows downstream from the filter/membrane, to the sample chamber(s). The balance of the sample (e.g., blood cells) remains at the filter/membrane. In various embodiments, the filter/membrane may be constructed from microporous polyethylene or microporous polytetrafluoroethylene. In another embodiment, the filter/membrane may be constructed from BTS-SP media available from Pall Corporation of East Hills, N.Y.
Additional information on sample elements, methods of use thereof, and related technologies may be found in U.S. Patent Application Publication No. U.S. 2005/0038357A1, published on Feb. 17, 2005, titled SAMPLE ELEMENT WITH BARRIER MATERIAL. The entire contents of this publication are hereby incorporated by reference herein and made a part of this specification.
In this section, there are disclosed a number of methods for sample-element referencing, which generally comprises compensating for the effects of the sample element on the measurement of analyte concentration. Any one or combination of the methods disclosed in this section may reside as program instructions in the memory 185 so as to be accessible for execution by the processor 180 of the analyte detection system 10. In addition, any one or combination of the methods disclosed in this section may be employed as the sample-element referencing operation 190i of various embodiments of the method 190 depicted in
Where employed as the sample-element referencing operation 190i of the method 190 (or where otherwise employed), any of the methods disclosed in this section may be performed in a wavelength-specific fashion, i.e. by computing a sample-element referenced transmittance, absorbance or optical density at each wavelength/band analyzed by the analyte detection system in question.
As discussed above, materials having some electromagnetic radiation absorption in the spectral range employed by the analyte detection system 10 can be used to construct some or all of the sample element 120. The accuracy of an analyte detection system, such as the system 10 disclosed herein, may be improved by accounting for any scattering or absorption phenomena attributable to the sample element when computing the concentration of the analyte(s) of interest. Such scattering or absorption due to imperfect transmission properties of the materials of the sample element may be overcome by determining at least one reference level of absorbance of the sample element and then removing the reference level from a subsequent measurement performed with the sample element. Devices and methods for overcoming imperfect transmission properties of materials employed in sample elements are now discussed with reference to
In one embodiment, an empty, unused sample element, such as the sample element 120, can be referenced by determining the reference level of absorbance/transmittance (and scattering) of the sample element 120. In certain embodiments, the method comprises positioning the sample chamber 200 of the sample element 120 within the sample beam Es which passes through the windows 202c, 202d. The analyte detection system 10 then determines a reference level of absorbance or transmittance by the windows 202c, 202d. A sample material is then drawn into the sample chamber 200. The sample beam Es is then passed through the windows 202c, 202d of the sample chamber 200 as well as the sample itself. The analyte detection system 10 determines an analytical level of absorbance or transmittance by the combination of the sample and the windows 202c, 202d. Upon determining the reference and analytical levels of absorbance or transmittance, the analyte detection system 10 can account for absorption/transmission effects of the material comprising the windows 202c, 202d when determining the concentration of the analyte(s) of interest. Analyzing the reference and analytical levels of absorbance or transmittance (in other words, accounting for the absorbance/transmittance effects of the material comprising the windows 202c, 202d) can comprise calculating an difference in optical density between the two. Alternatively, analyzing the levels can comprise calculating a ratio of the analytical level of transmission to the reference level of transmission.
The difference-calculation alternative is employed where the sample element referencing method is performed in the absorbance or optical density domain, and the ratio-calculation alternative is employed where the method is performed in the transmittance domain. The resulting data set (typically, an absorbance or transmittance spectrum assembled from sample-element referenced absorbance/transmittance measurements taken at each wavelength/band analyzed by the detection system 10) can then be analyzed to compute the concentration of the analyte(s) of interest in the sample. This concentration analysis may be performed by employing any suitable method, including but not limited to any of the various computational algorithms discussed in further detail in Section IV below. For example, any of the methods disclosed below for determining analyte concentration(s) independent of the optical pathlength through the sample, may be employed.
As illustrated in
In one embodiment, one or more of the outer surfaces of one or more of the windows 304a, 304b, 306a, 306b is textured. This may be done by, for example, sanding the surface(s) in question, and/or molding or otherwise constructing them to have a relatively non-smooth surface finish. Depending on the materials employed to construct the sample element, texturing may improve the optical qualities of the sample element by reducing fringing. This texturing may be employed with any of the embodiments of the sample element disclosed herein by, for example, texturing one or both of the outer surfaces of the windows 202c, 202d of the sample element 120.
In one method of operation, the sample element 302 is coupled with an analyte detection system 10 which utilizes a single beam of electromagnetic radiation for referencing the sample element 302 and for measuring the concentration of an analyte in the sample. A sample is drawn into the referencing chamber 304 (in those embodiments where the referencing chamber is of sufficient pathlength or volume) and into the sample chamber 306. The sample element 302 is placed in a reference position within the analyte detection system 10 wherein the referencing chamber 304 and referencing windows 304a, 304b reside within an optical path of a reference beam 308 of electromagnetic radiation. The reference beam 308 is then passed through the referencing chamber 304 (and, where applicable, that portion of the sample contained therein), and referencing windows 304a, 304b. The analyte detection system 10 determines a reference level of absorbance or transmittance of the reference beam 308 due to absorbance or transmittance by the combination of (any) sample within the referencing chamber 304 and the referencing windows 304a, 304b. The sample element 302 is placed into an analytical position wherein the sample chamber 306 and sample windows 306a, 306b reside within the optical path of an analytical beam 310. The analytical beam 310 is then passed through the sample-filled sample chamber 306 and sample windows 306a, 306b. The analyte detection system 10 determines an analytical level of absorbance or transmittance of the analytical beam 310 due to absorbance or transmittance by the combination of the sample within the sample chamber 306 and the sample windows 306a, 306b. In one embodiment, reference and analytical levels of absorbance or transmittance are measured at each wavelength/band analyzed by the analyte detection system 10.
Upon determining the reference and analytical levels of absorbance or transmittance, the analyte detection system 10 can account for absorbance or transmittance effects of the material comprising the sample element 302 when determining the concentration of the analyte(s) of interest in the sample. Analyzing the reference and analytical levels of absorbance or transmittance (in other words, accounting for the absorbance or transmittance effects of the material comprising the sample element 302) can comprise calculating a difference between the two. Alternatively, analyzing the levels can comprise calculating a ratio of the analytical level to the reference level.
The difference-calculation alternative is employed where the sample element referencing method is performed in the absorbance or optical density domain, and the ratio-calculation alternative is employed where the method is performed in the transmittance domain. Where reference and analytical levels of absorbance or transmittance have been measured in each of a series of wavelengths/bands, the difference calculation or ratio calculation is performed on the (reference level, analytical level) pair measured at each wavelength/band in the series.
The resulting data set (for example, an absorbance or transmittance spectrum assembled from sample-element referenced absorbance/transmittance measurements taken at each wavelength/band analyzed by the detection system 10) can then be analyzed to compute the concentration of the analyte(s) of interest in the sample. This concentration analysis may be performed by employing any suitable method, including but not limited to any of the various computational algorithms discussed in further detail in Section IV below. For example, any of the methods disclosed below for determining analyte concentration(s) independent of the optical pathlength through the sample, may be employed.
Where significant differences arise between the thicknesses of the first referencing window 304a and first sample window 306a, or between the thicknesses of the first referencing window 304a and first sample window 306a, the absorbance/transmittance data output by the ratio-calculation/difference calculation procedure may “include” some of the absorbance/transmittance aspects of the window material. Accordingly, where desired various embodiments of the methods disclosed in Section IV below for removing non-analyte contributions from absorption data, may be employed when analyzing the absorbance/transmittance data to determine analyte concentration.
In another method of operation depicted in
Upon determining the reference and analytical levels of absorbance or transmittance, the analyte detection system 10 can account for absorbance or transmittance effects of the material comprising the sample element 302 when determining the concentration of the analyte(s) of interest in the sample. Analyzing the reference and analytical levels of absorbance or transmittance (in other words, accounting for the absorbance or transmittance effects of the material comprising the sample element 302) can comprise calculating a difference between the two. Alternatively, analyzing the levels can comprise calculating a ratio of the analytical level to the reference level.
The difference-calculation alternative is employed where the sample element referencing method is performed in the absorbance or optical density domain, and the ratio-calculation alternative is employed where the method is performed in the transmittance domain. Where reference and analytical levels of absorbance or transmittance have been measured in each of a series of wavelengths/bands, the difference calculation or ratio calculation is performed on the (reference level, analytical level) pair measured at each wavelength/band in the series.
The resulting data set (for example, an absorbance or transmittance spectrum assembled from sample-element referenced absorbance/transmittance measurements taken at each wavelength/band analyzed by the detection system 10) can then be analyzed to compute the concentration of the analyte(s) of interest in the sample. This concentration analysis may be performed by employing any suitable method, including but not limited to any of the various computational algorithms discussed in further detail in Section IV below. For example, any of the methods disclosed below for determining analyte concentration(s) independent of the optical pathlength through the sample, may be employed.
Where significant differences arise between the thicknesses of the first referencing window 304a and first sample window 306a, or between the thicknesses of the first referencing window 304a and first sample window 306a, the absorbance/transmittance data output by the ratio-calculation/difference calculation procedure may “include” some of the absorbance/transmittance aspects of the window material. Accordingly, where desired various embodiments of the methods disclosed in Section IV below for removing non-analyte contributions from absorption data, may be employed when analyzing the absorbance/transmittance data to determine analyte concentration.
In certain embodiments, a sample element may be referenced so as to overcome transmission properties of the materials comprising the sample element by drawing a sample into the sample element and then compressing a sample chamber of the sample element, thereby changing the separation (i.e., pathlength) between the inner surfaces of the sample chamber by a predetermined amount. Such embodiments use a deformable sample element and controllably change the pathlength of the beam of electromagnetic radiation passing through the material of; and/or the sample within, the sample chamber. The change in pathlength facilitates distinguishing the absorbance or transmittance by the material of the sample element from the absorbance or transmittance by the sample within the sample chamber, by using any of the analysis methods (i.e., difference-calculation, ratio-calculation) disclosed above.
As shown, the sample element 402 is positionable within the analyte detection system 406 such that a sample chamber 404 of the sample element 402 is positioned between the compressors 408, 409. Each compressor 408, 409 has a hollow portion 412 aligned with the major axis of the compressor to allow for substantially unimpeded passage of a beam of electromagnetic radiation through the compressors 408, 409 and through the sample chamber 404. In one embodiment, the compressors 408, 409 may have a circular cross-section (i.e., the compressors 408, 409 are formed as cylinders). In other embodiments, the compressors 408, 409 can have other cross-sectional shapes. Preferably, the sample element 402 is made of a material which is sufficiently pliable to allow for compression by the compressors 408, 409.
As illustrated in
The beam 443 of electromagnetic radiation is passed through the sample chamber 404 to yield a first measurement of absorbance or transmittance by the combination of the sample and the sample element 402 once the sample is drawn into the sample chamber 404. In certain embodiments, the sample is drawn into the sample chamber 404 of the sample element 402 prior to insertion of the sample element 402 into the analyte detection system 406. In other embodiments, the sample is drawn into the sample chamber 404 after the sample element 402 is positioned in the analyte detection system 406.
After the first measurement of absorbance or transmittance is taken, the analyte detection system 406 compresses the sample element 402 by increasing the forces 410, 411 exerted by the compressors 408, 409. These increased forces 410, 411 more strongly compress the sample element 402. In response to this stronger compression, the optical pathlength through the sample element 402 is modified. Preferably, the sample element 402 undergoes plastic deformation due to the compression forces 410, 411, while in other embodiments, the deformation is elastic.
Once the optical pathlength through the sample element 402 is modified, a second measurement of absorbance or transmittance by the combination of the sample and the sample element 402 is taken. The analyte detection system 406 then computes a sample-element referenced absorbance or transmittance of the sample based on the first measurement of absorbance or transmittance at the first pathlength and the second measurement of absorbance or transmittance at the second pathlength, using any of the analysis methods (i.e., difference-calculation, ratio-calculation) disclosed above. Changing the optical pathlength facilitates distinguishing the absorbance or transmittance by the material comprising the sample element 402 from the absorbance or transmittance by the sample within the sample chamber 404. Thus, the analyte detection system 406 provides a measurement of the absorbance or transmittance by the sample which is substantially free of contributions from the absorbance or transmittance of the material comprising the sample element 402. Such measurements can increase the accuracy of the analyte concentration measurements performed by the system 10 based on the sample-element referenced absorbance or transmittance measurements. These analyte concentration measurements may be performed by employing any suitable method, including but not limited to any of the various computational algorithms discussed in further detail in Section IV below. For example, any of the methods disclosed below for determining analyte concentration(s) independent of the optical pathlength through the sample, may be employed.
In the embodiment illustrated by
The compressor windows 512, 513 are preferably at least partially optically transmissive in the range of electromagnetic radiation comprising the beam 443. In one embodiment, one or both of the compressor windows 512, 513 comprises a material that is substantially completely transmissive to the electromagnetic radiation comprising the beam 443. In yet another embodiment, the absorbance of the material of one or both of the compressor windows 512, 513 is not negligible, but it is known and stable for a relatively long period of time, and is stored in memory (not shown) of the analyte detection system 506 so that the system 506 can remove the contributions due to absorbance or transmittance of the material from measurements of the concentration of the analyte(s) of interest. In another embodiment, the absorbance of one or both of the compressor windows 512, 513 is stable for only a relatively short period of time, but the analyte detection system 506 is configured to observe the absorbance of the material and substantially eliminate it from the analyte measurement before the material properties change significantly.
In various embodiments, the compressor windows 512, 513 may be formed from silicon, germanium, polyethylene, or polypropylene, and/or any other suitable infrared-transmissive material.
In certain embodiments, a sample element is referenced so as to overcome transmission properties of the material comprising the sample element by drawing a sample such as whole blood into the sample element and then compressing the sample element to cause the sample chamber of the sample element to expand in a controlled manner, thereby controllably increasing the separation between the inner surfaces of the sample chamber. In this way, the compression of the sample element increases the optical pathlength through the sample chamber. The change in the optical pathlength facilitates distinguishing the absorbance or transmittance by the material comprising the sample element from the absorbance or transmittance by the sample within the sample chamber.
As illustrated in
The sample element 302 further comprises a first strut 320 disposed in the referencing chamber 304 and extending from the first referencing window 304a to the second referencing window 304b. In addition, a second strut 322 is disposed in the sample chamber 306 and extends from the first sample window 306a to the second sample window 306b. The struts 320, 322 are preferably oriented in the chambers 304, 306 so that they extend generally parallel to an optical axis of a beam of energy passed through either of the chambers 304, 306, when the sample element 302 is employed in measuring analyte concentrations. For example, when the sample element 302 is placed in the analyte detection system 10, the strut(s) 320, 322 extend generally parallel to the major axis X and/or the energy beam E.
The struts 320, 322 depicted in
In the illustrated embodiment, the struts 320, 322 comprise cylindrical members (i.e. having a circular cross-section); however, any other suitable cross-sectional shape (including without limitation oval, square, rectangular, triangular, etc.) may be employed. In the illustrated embodiment, the struts 320, 322 maintain a substantially constant cross-section as they extend from the first window 304a/306a to the second window 304b/306b; however, a varying cross-section may be employed.
In the embodiment shown in
In one embodiment, each of the struts 320, 322 is substantially opaque to the wavelength(s) of energy employed by the analyte detection system (such as the system 10) with which the sample element 302 is employed. For example, the struts 320, 322 may be formed from a material which is substantially opaque to the wavelength(s) of interest, in the source intensity range employed by the detection system, and when formed in a pathlength less than or equal to the shorter of the struts 320, 322. In another example, the struts may be formed from a material which does not meet the above criteria, but a mask layer (not shown) may be positioned in each strut, or in or on one of the windows 304a/304b and one of the windows 306a/306b, in axial alignment with each strut. The mask layers are substantially opaque to the wavelength(s) of interest and are shaped and sized to conform to the (largest) cross-section of the corresponding struts, so as to substantially prevent passage of the energy beam E through the struts 320, 322. In still further embodiments, any suitable structure may be employed to substantially prevent passage of the energy beam E through the struts 320, 322.
By making the struts 320, 322 substantially opaque to the wavelength(s) of interest, or by otherwise preventing prevent passage of the energy beam E through the struts 320, 322, the absorbance/transmittance of the struts drops out from the absorbance/transmittance data when the difference or ratio is computed of the absorbance/transmittance measured in each chamber 304, 306. In other words, by making the absorbance/transmittance of the struts 320, 322 independent of the length of the struts, their absorbance/transmittance can be accounted for in computing analyte concentrations, despite their difference in length. In another embodiment, a similar result can be obtained by otherwise constructing the struts 320, 322 to have substantially equal absorbance or transmittance, but without making the struts 320, 322 opaque.
In yet another embodiment, the strut(s) 320, 322 may be formed from a material which is highly transmissive of the wavelength(s) of interest. For example, where infrared wavelengths are employed in the measurement of analyte concentrations, the strut(s) may be formed from silicon, germanium, polyethylene, polypropylene, or a combination thereof.
It is further contemplated that one or more struts of the type presently disclosed may be employed in the sample chamber 200 of the sample element 120, so as to extend from the upper window 202c to the lower window 202d.
The sample element 302 depicted in
In other embodiments, a similar stiffening layer may be secured to the upper side of the sample element 302, instead of or in addition to the stiffening layer 340 depicted in
It is further contemplated that one or more stiffening layers similar to the layer 340 may be employed with the sample element 120 disclosed above, secured to one or both of the first and third layers 220, 240.
The sample element 302 depicted in
In any of these embodiments, any suitable size, shape and number of ribs may be employed, other than those depicted in
The ribs 350 advantageously assist in preserving the planarity of the windows 304a, 304b, 306a, 306b, thereby enhancing the accuracy of analyte-concentration measurements taken with the sample element 302. Although various computational algorithms are disclosed below for preserving measurement accuracy despite imperfections in sample-element geometry (e.g., pathlength, window planarity, window parallelism), the ribs 350 may be employed instead of or in addition to various combinations of such algorithms when measuring analyte concentrations.
This section discusses a number of computational methods or algorithms which may be used to calculate the concentration of the analyte(s) of interest in the sample S, and/or to compute other measures that may be used in support of calculations of analyte concentrations. Any one or combination of the algorithms disclosed in this section may reside as program instructions in the memory 185 so as to be accessible for execution by the processor 180 of the analyte detection system 10 to compute the concentration of the analyte(s) of interest in the sample, or other relevant measures. Alternatively, any one or combination of the algorithms disclosed in this section may be executed by or in connection with a Fourier Transform Infrared Spectrometer (FTIR) device, such as the SPECTRUM ONE model available from Perkin-Elmer Inc., of Wellesley, Mass., for determining analyte concentrations or other measures. In addition, any one or combination of the algorithms disclosed in this section may be employed in connection with any of the embodiments of the method 190 depicted in
A. Methods for Determining Blood Analyte Concentrations
In many measurements, the contribution from the analyte of interest (e.g., glucose) to the measured absorption spectrum is often only a small percentage of the contribution from other substances within the sample. For example, blood by volume is typically composed of about 70% water, about 30% solids, mostly protein, and only about 0.1% glucose. Blood also includes other species such as urea, alanine, and in some cases alcohol or other sugars such as fructose. Therefore, blood glucose measurements are highly sensitive and vulnerable to inaccuracies.
If an accurate glucose measurement is desired, the characteristics of each of the different blood constituents should be considered. Because the sample absorption at any given wavelength is a sum of the absorptions of each component of the sample at that wavelength, IR absorption measurements are complicated by the presence of these other components. Consequently, to allow effective compensation and adjustments to measured IR absorption for the presence of other blood components, it is helpful to understand which constituents are present in the sample, understand their effects on the analyte that is being measured (such as glucose), and correct for any differences that intrinsic and measuring-device-related variables may cause.
Advantageously, absorption data in the mid-IR spectral region (for example, about 4 microns to about 11 microns) are used. Although water is the main contributor to the total absorption across this spectral region, the peaks and other structures present in the blood spectrum from about 6.8 microns to 10.5 microns are due to the absorption spectra of other blood components. The 4 to 11 micron region has been found advantageous because glucose has a strong absorption peak structure from about 8.5 to 10 microns, whereas most other blood constituents have a low and flat absorption spectrum in the 8.5 to 10 micron range. The main exceptions are water and hemoglobin, both of which absorb fairly strongly in this region, and which are also the two most significant blood components in terms of concentration. Certain embodiments of the techniques described herein are thus directed to removing the contributions of water and hemoglobin from this spectral region to resolve the contribution, and thus concentration, of glucose in the sample.
B. Pathlength-Insensitive Determinations of Blood Analyte Concentrations
In certain embodiments, a method determines an analyte concentration in a sample comprising the analyte and a substance. The method comprises providing an absorption spectrum of the sample, with the absorption spectrum having an absorption baseline. The method further comprises shifting the absorption spectrum so that the absorption baseline approximately equals a selected absorption value in a selected absorption wavelength range. The method further comprises subtracting a substance contribution from the absorption spectrum. Thus, the method provides a corrected absorption spectrum substantially free of a contribution from the substance.
In certain embodiments, providing the absorption spectrum comprises providing the transmittance spectrum of the sample, with the transmittance spectrum having a transmittance baseline. In certain embodiments, the transmittance spectrum of the sample is provided by transmitting at least a portion of an infrared signal through the sample. The infrared signal comprises a plurality of wavelengths. The portion of the infrared signal transmitted through the sample is measured as a function of wavelength. Various configurations and devices can be used to provide the transmittance spectrum in accordance with embodiments described herein.
In certain embodiments, the transmittance baseline is defined to be the value of the transmittance spectrum at wavelengths at which transmittance is a minimum. For blood, this value is typically at about 6.1-6.2 microns where water and hemoglobin both are strong absorbers. While the transmittance spectrum from the sample at these wavelengths is expected to be nearly zero, various effects, such as instrumental error and thermal drift, can result in a nonzero contribution to the transmittance baseline. In addition, effects such as instrumental error and thermal drift can result in a wavelength shift of known features in the transmittance spectrum from the expected wavelengths of these features.
In certain such embodiments, providing the absorption spectrum comprises shifting the transmittance spectrum so that the transmittance baseline approximately equals zero in a selected transmittance wavelength range. In certain embodiments in which the sample comprises blood, the selected transmittance wavelength range comprises wavelengths at which the transmittance is a minimum. In certain such embodiments, the selected transmittance wavelength range comprises wavelengths between approximately 6 microns and approximately 6.15 microns. In other such embodiments, the selected transmittance wavelength range comprises wavelengths between approximately 12 microns and approximately 13 microns. The transmittance spectrum at these wavelengths may be partially affected by contributions from various blood components that are present at low concentration levels. In still other such embodiments, the selected transmittance wavelength range comprises wavelengths approximately equal to 3 microns. Each of these wavelengths corresponds to a strong water absorption peak.
In embodiments in which there is a nonzero contribution to the transmittance baseline, the transmittance spectrum may be shifted. In certain embodiments, the transmittance spectrum is shifted so that the transmittance spectrum in the wavelength range of 6 to 6.2 microns is approximately equal to zero. In embodiments in which known features are shifted in wavelength from their expected wavelengths, the transmittance spectrum can be shifted in wavelength. In addition, the shifting of the transmittance spectrum can be performed nonlinearly (e.g., shifting different wavelengths by differing amounts across the transmittance spectrum).
Providing the absorption spectrum further comprises determining the absorption spectrum from the transmittance spectrum. In certain embodiments, the relation between the transmittance spectrum and the absorption spectrum is expressed as:
where λ is the wavelength, A(λ) is the absorption as a function of wavelength, and T(λ) is the transmittance as a function of wavelength.
In certain embodiments, the method comprises shifting the absorption spectrum so that its absorption baseline approximately equals a selected absorption value (such as 0, 0.5, 1, etc.) in a selected absorption wavelength range. In certain embodiments, the absorption baseline can be selected to be defined by a portion of the absorption spectrum with low absorption. In certain embodiments in which the sample comprises blood, the selected absorption wavelength range comprises wavelengths between approximately 3.8 microns and approximately 4.4 microns. In certain other embodiments, the selected absorption wavelength range comprises wavelengths between 9 microns and approximately 10 microns.
In certain other embodiments in which the sample comprises blood, the absorption baseline is defined to be the magnitude of the absorption spectrum at an isosbestic wavelength at which water and a whole blood protein have approximately equal absorptions. In such embodiments, the absorption spectrum is shifted to a selected value at the isosbestic wavelength by adding or subtracting a constant offset value across the entire wavelength spectral data set. In addition, the shifting of the absorption spectrum can be performed nonlinearly (e.g., shifting the portions of the absorption spectrum in different wavelength ranges by different amounts). Shifting the absorption spectrum such that the absorption is set to some value (e.g., 0) at a protein-water isosbestic point preferably helps remove the dependence on hemocrit level of the overall spectrum position relative to zero.
The effective isosbestic point can be expected to be different for different proteins in different solutions. Exemplary whole blood proteins include, but are not limited to, hemoglobin, albumin, globulin, and ferritin. These isosbestic wavelengths can be used to obtain a current measure of the effective optical pathlength in the filled cuvette, either before or during measurements at other wavelength ranges.
Such information is very useful in subsequent calculations for compensation of instrument-related pathlength non-linearities. Because the measured absorption of the protein and water are identical at the isosbestic wavelength, the measured absorption at the isosbestic wavelength is independent of the ratios of the protein concentration and the water concentration (hemocrit level). At an isosbestic wavelength, for a given sample volume, the same amount of absorption would be observed whether the sample was entirely water, entirely protein, or some combination of the two. The absorption at the isosbestic wavelength is then an indication of the total sample volume, independent of the relative concentrations of water and protein. Therefore, the observed absorption at an isosbestic wavelength is a measure of the pathlength of the sample only. In certain embodiments, the observed absorption at an isosbestic wavelength can be useful for measuring the effective optical pathlength for a sample. As a result, various embodiments of the above-described method may be employed to accurately determine the concentration of analyte(s) of interest in a sample independent of optical pathlength, i.e. without need for prior knowledge of the pathlength and/or without requiring that the sample chamber of the sample element conform closely to a specified or expected pathlength. Additionally, such information can be used in subsequent calculations for compensation of instrument-related pathlength nonlinearities. In certain embodiments, these measurements can be made before or concurrently with absorption measurements in other wavelength ranges.
C. Subtraction of Non-Analyte Contributions from Absorption Data
One goal of the spectroscopic analysis can be to derive the ratio of the analyte volume (for example, glucose volume) to the total blood volume. The process of measuring a glucose concentration can include subtracting one or more contributions to the absorption spectrum from other substances in the blood that interfere with the detection of the glucose. In certain embodiments, a reference substance absorption spectrum is provided and is scaled by multiplying it by a scaling factor. The scaled reference substance absorption spectrum is subtracted from the measured absorption spectrum. This procedure thus preferably provides the corrected absorption spectrum which is substantially free of a contribution from the substance. Such procedures can be used to subtract the absorption contributions of water and/or hemoglobin, as well as other constituents of blood. In addition, the scaling factor provides a measure of the absorption due to the substance of the reference substance absorption spectrum. As described more fully below, in embodiments in which multiple scaling factors are determined for multiple substances, ratios of the scaling factors provide information regarding the concentration ratios of the substances in question. These determinations of the concentration ratios are substantially independent of the optical pathlength through the sample. Such concentration ratios can be used to determine the concentration of a selected substance within the sample regardless of the optical path length through the sample.
In certain embodiments, the measured absorption spectrum can be further corrected for other contributions which are not due to the analyte of interest. For example, alcohol is a potentially interfering substance with the glucose measurement because the absorption of alcohol is similar to that of glucose in the wavelength range of interest. It is observed that the peak height ratio of the absorption peak at about 9.6 microns to the absorption peak at about 9.2 microns for pure glucose is approximately 1.1-1.2, and the ratio for pure alcohol is approximately 3.0-3.2. This ratio of peak heights varies between these two values for absorption spectra for mixtures of glucose and alcohol. Thus, the peak height ratio can be used to determine the relative concentrations of alcohol and glucose. The contribution from alcohol can then be subtracted from the measured absorption spectrum.
In certain embodiments, the measured absorption spectrum can be corrected for contributions from free protein, which has an absorption peak centered around 7.1 microns. In certain other embodiments, the measured absorption spectrum can be further corrected for contributions from a boundary layer between water and a whole blood protein. Features in the measured absorption spectrum due to components of the boundary layer arise from interactions between the water and whole blood protein. These spectral features are ascribed to “bound” components or hydrated protein. The corresponding contributions across the measured absorption spectrum can be corrected by subtracting the appropriate scaled reference absorption, such that the corrected absorption spectrum is approximately zero for a selected range of wavelengths. In certain embodiments, the range of wavelengths is between about 7.0 and 7.2 microns, or alternatively between 7.9 and 8.1 microns, or alternatively at a combination of wavelength ranges.
Temperature also affects the correct subtraction of the water contribution to the total spectrum because the absorption spectrum of water changes with temperature changes. It is therefore advantageous for the system to store several different water reference spectra, with each one applicable to a selected temperature range. The appropriate reference would be selected for scaling and subtraction based on the temperature of the sample. In some embodiments, hardware such as thermocouples, heaters, and the like may be provided to directly measure or control the temperature of the sample. Although this approach may be suitable at times, it can be difficult to accurately measure and control the blood temperature as the sample size is very small, and the actual blood temperature may vary from the cuvette temperature or the ambient temperature surrounding the cuvette.
The contribution of temperature to the absorption spectra can alternatively be addressed by analyzing the sample spectrum itself, because different parts of the water absorption spectrum are affected by temperature by different amounts. For example, the absorbance difference of the water absorption spectrum between about 4.9 microns and 5.15 microns is not very dependent on temperature, whereas the absorbance difference between 4.65 microns and 4.9 microns is highly temperature dependent. As temperature changes for a given sample with constant water concentration, the absorbance difference between 4.65 and 4.9 microns will change a lot, and the absorbance difference between 4.9 and 5.15 microns will not change much at all. Thus, the ratio of the absorbance difference between two points having high temperature dependence (e.g., 4.65 and 4.9 microns) to the absorbance difference between two points having low temperature dependence (e.g., 4.9 and 5.15 microns) can be used as a measure of temperature. Once this measurement is made, an appropriate selection from several different stored water reference curves can be made.
In certain embodiments, the reference substance absorption spectrum is provided by correcting a stored spectrum for wavelength nonlinearities. For example, where the substance comprises water, knowledge of the optical pathlength (based on the total sample absorption at one or more isosbestic wavelengths) as well as the measured absorption at one or more wavelengths dominated by water absorption (e.g., between approximately 4.5 and 5 microns) can be used to correct a stored reference water absorption spectrum for wavelength nonlinearities across the spectrum. Such corrections of the stored reference spectrum are advantageous for reducing distortions in the final results. Similarly, prior knowledge of optical pathlength based on total sample absorption at an isosbestic wavelength, as well as on total protein absorption in a selected wavelength range (e.g., 7.0-7.2 microns, or 7.9-8.1 microns) allows for the modification of a reference protein absorption spectrum that is compensated for nonlinearities.
In certain embodiments, after correcting the measured absorption spectrum for contributions of one or more substances, the corrected absorption spectrum is fitted with reference analyte spectral data to provide a measure of the analyte concentration. The reference analyte spectral data can include data at a wavelength near an analyte absorption maximum. For example, the absorption spectrum of glucose includes various peaks, with the two largest peaks at wavelengths of approximately 9.25 and 9.65 microns, respectively. The absorption difference of the corrected absorption spectrum between a wavelength of about 8.5 microns and a wavelength of approximately 9.65 microns can provide a measure of the glucose concentration in the blood sample. Following the definition of glucose in blood (i.e., a measure of glucose per volume of the sample), a useful measure for glucose concentration is preferably obtained from algorithmically-derived infrared quantities by dividing the final glucose quantity by total water, total protein, or alternatively a combination of both.
Although the above discussion focuses on data sets comprising measurements over the entire range of IR wavelengths, it will be appreciated that it is not necessary to obtain data across the entire spectrum, but only at the discrete wavelengths used in the analysis. In certain embodiments where water and hemoglobin contributions are subtracted from a whole blood spectrum to find glucose concentration, as little as ten or fewer total measurements are needed. Additional components to be subtracted may require one or two more measurements each.
For example, to characterize the water contribution, measurements at about 4.7 microns and 5.3 microns may be obtained. For characterizing hemoglobin, measurements at about 8.0 and 8.4 microns may be obtained. The glucose characterization may involve a measure of the difference between about 8.5 microns and 9.6 microns. This is six values, two for each component. In embodiments where it is desired to zero the transmittance curve and shift the absorbance values, it may be desirable to further make transmittance measurements at about the 6.1 micron water absorbance peak and the 4.1 micron water/protein isosbestic point. As described above, the addition of another data point at about 4.9 microns allows the determination of temperature. Another measurement at the lower alcohol peak of about 9.25 microns can be used to compensate the glucose measurement for alcohol content as well as is also described above. In certain embodiments, the values of optical density at these six wavelengths can be expressed as six linear equations which can be solved to yield the glucose concentration path length and the ratio of glucose volume to total blood volume.
In certain embodiments, the method uses the optical density (OD), which can be expressed as:
ODi=(cwαwi+chαhi+cgαgi)·d
where:
In certain embodiments, the method uses three two-wavelength sets. The first set is in the wavelength region where water absorption dominates. The second set is in a region where water and hemocrit absorptions dominate, and the third set in a region where absorptions from all three components dominate. In certain embodiments, the calculations are based on OD differences of each wavelength pair to reduce or minimize offsets and baseline drift errors. Absorption values for the three components at each of the six wavelengths are shown in Table 1:
Substituting these values from Table 1 into the equation for OD yields the following relations:
OD1=cwαw1d;
OD2=cwαw2d;
OD3=(cwαw3+chαh3)·d;
OD4=(cwαw4+chαh4)·d;
OD5=(cwαw5+chαh5+cgαg5)·d; and
OD6=(cwαw6+chαh6+cgαg6)·d.
Certain embodiments of the method comprise computing the quantity A which is equal to the product of the water concentration and the path length. The quantity A can be termed the “water scaling factor,” and can be expressed by the following relation:
In certain embodiments in which the values of water absorption at the two wavelengths is known or provided to the system, this ratio of the difference of two measured absorption values with the difference of two reference absorption values at the same wavelengths yields a water scaling factor A indicative of the amount of water in the sample.
Using A and the water absorptions at each wavelength, the “water free” OD can then be calculated and expressed by the following relation:
ODi′=ODi−Aαwi.
In this way, the “water free” OD value equals the measured OD value minus the scaled reference absorption value for water. Combining the above equations yields the following relations:
OD3′=chαh3·d;
OD4′=chαh4·d;
OD5′=(chαh5+cgαg5)·d; and
OD6′=(chαh6+cgαg6)·d.
In certain embodiments, the “water free” absorptions at wavelengths 3 and 4 are used to calculate the quantity B which is proportional to the product of the hemocrit concentration and path length. The quantity B can be termed the “hemocrit scaling factor,” and can be expressed by the following relation:
In certain embodiments in which the values of hemocrit absorption at the two wavelengths is known or provided to the system, this ratio of the difference of two “water free” OD values with the difference of two reference absorption values for hemocrit at the same wavelengths yields a hemocrit scaling factor B indicative of the amount of hemocrit in the sample.
By using B and the hemocrit absorptions at each wavelength, the “glucose only” OD is calculated in certain embodiments to be expressed by the following relation:
ODi″=ODi′−Bαhi.
In this way, the “glucose only” OD value equals the measured OD value minus the scaled reference absorption values for water and for hemocrit.
From the above equations, the following relations can be calculated:
ODS″=cgαg5d; and
OD6″=cgαg6d.
The glucose concentration path length product, given by the quantity C which can be termed the “glucose scaling factor,” and which can be expressed by the following relation:
In certain embodiments in which the values of glucose absorption at the two wavelengths is known or provided to the system, this ratio of the difference of two “glucose only” OD values with the difference of two reference absorption values for glucose at the same wavelengths yields a glucose scaling factor C indicative of the amount of glucose in the sample.
The desired ratio of glucose volume to total blood volume can then be expressed (using the relation: cw+ch+cg=1) by the following relation:
By taking the ratio of the glucose scaling factor to the sum of the water scaling factor, the hemocrit scaling factor, and the glucose scaling factor, the resulting concentration ratio cg is substantially independent of the path length of the sample. Thus, certain embodiments described herein provide a method of determining the glucose content of a blood sample independent of the path length of the blood sample.
D. System and Temperature Effects on Absorption
In certain embodiments, the resulting absorption spectrum (e.g., after being corrected for instrumental drift, optical pathlength, distortions, and contributions from major components) can be fitted with a reference glucose absorption spectrum to remove the glucose contribution. This absorption spectrum can be used further for individual determination of residual components. In certain embodiments, the residual components include high molecular weight substances, including but not limited to, other proteins, albumin, hemoglobin, fibrinogen, lipoproteins, and transferrin. In certain embodiments, the residual components include low molecular weight substances, including but not limited to, urea, lactate, and vitamin C. The final glucose measure can be corrected for the presence of such lower level potentially interfering substances by subtracting reference spectra of specific substances, such as urea, from the residual data.
1. Expression of Integral Optical Density as Sum of Terms
In certain embodiments, various non-analyte contributions to the measured absorption spectrum can be determined. For a water-filled cuvette irradiated by light transmitted through a filter “n”, the optical density can be expressed as being equal to the average water absorption through the filter multiplied by the pathlength, plus a correction term due to the finite filter width and shape, plus a correction term due to the cuvette shape, and a cross-term resulting from finite filter width and cuvette shape by the following relation:
2. Temperature effects on optical density
In addition, the optical density ODn can be expressed to include contributions to the measured absorption spectrum from changes in water temperature, changes in filter temperature, and a cross-term resulting from water and filter temperature changes by the following relation:
E. Subtraction of System and Temperature Effects From Absorption Data
The analysis of the absorption data preferably uses a finite number of absorption measurements to determine the path length, water temperature, filter temperature and cuvette shape. In certain embodiments, the analysis utilizes four OD measurements which, assuming Tn=0 and αn
=
αon
, are expressed as a set of linear equations to be solved expressed by the following relation:
The solution of this set of linear equations can provide an initial estimate of the parameters (davg, ΔTw, ΔTf, A) which are used to evaluate the non-linear terms (T1 . . . T4). The next estimate of (davg, ΔTw, ΔTf, A) can be found by solving the following relation:
This process can be repeated until estimates of path length, water temperature, filter temperature and cuvette non-parallelism (i.e., the degree to which opposed walls/windows of the sample chamber deviate from parallel) converge.
Measurements using this approach may not deliver the desired accuracy over the entire range of temperature and cuvette/sample chamber shape. Other approaches may be used to yield more stable results. One such alternative approach is based on rewriting the equations above as follows:
Rearranging the terms of these relations yields the following relation:
Embodiments in which this relation is used to analyze the absorption data are described below.
1. Water Temperature, Filter Temperature, Cuvette Shape Analysis
In certain embodiments, the water temperature, filter temperature, and cuvette shape are analyzed. In such embodiments, the analysis comprises “step 1” in which transmission measurements, filter parameters and water spectral properties are inputted:
Certain embodiments of the analysis further comprise “step 2” in which optical densities and filter constants are calculated:
In certain embodiments, the analysis further comprises “step 3” in which the non-linear filter terms and cuvette distortion matrix element are estimated using the following relations:
αn
2=
αon
2, and
Sn=0.
In certain embodiments, the analysis further comprises “step 4” in which the analysis solves for (ΔTw, ΔTf, A) as a function of path length d using (OD1, OD2, OD3) and (OD2, OD3, OD4). The values of (davg, ΔTw, ΔTf, A) are estimated by finding value of d where solutions for (ΔTw, ΔTf, A) are same for both sets of transmission measurements:
In certain embodiments, the analysis further comprises “step 5” in which new estimates of absorption and non-linear terms are calculated:
In certain embodiments, the analysis further comprises “step 6” in which “step 4” and “step 5” are repeated until the solution converges to a desired accuracy.
2. Water Temperatures, Filter Temperatures Parallel Cuvette Analysis
In certain other embodiments, the water temperature and filter temperature are analyzed for a parallel cuvette (i.e., one in which opposed walls of the sample chamber are substantially parallel). In such embodiments, the analysis comprises “step 1” in which transmission measurements, filter parameters and water spectral properties are inputted:
Certain embodiments of the analysis further comprise “step 2” in which optical densities and filter constants are calculated:
In certain embodiments, the analysis further comprises “step 3” in which the non-linear filter terms and cuvette distortion matrix element are estimated using the following relations: αn
2=
αon
2,
and
Sn=0.
In certain embodiments, the analysis further comprises “step 4” in which the analysis solves for (ΔTw, ΔTf) as a function of path length d using (OD1, OD2) and (OD2, OD3). The values of (davg, ΔTw, ΔTf) are estimated by finding values of d where solutions for (ΔTw, ΔTf) are same for both sets of transmission measurements:
In certain embodiments, the analysis further comprises “step 5” in which new estimates of absorption and non-linear terms are calculated:
In certain embodiments, the analysis further comprises “step 6” in which “step 4” and “step 5” are repeated until the solution converges to a desired accuracy.
F. Contribution to Analyte Concentration Errors by Instrument Factors
Transmission data measured at each wavelength by certain apparatuses are typically affected by a combination of instrument factors and blood properties. The instrument factors include, but are not limited to, filter temperature, cuvette shape and filter characteristics (e.g., center wavelengths, temperature sensitivity, bandwidth, shape). The blood properties include, but are not limited to, blood temperature, the relative concentrations of the blood components and scattering. Before the transmission data are used to calculate analyte (e.g., glucose) concentration, the instrument factors are preferably determined and corresponding corrections are preferably made for each transmission value. As described above in relation to transmission measurements, each of the instrument factors can influence the transmission of a water-filled cuvette. In certain embodiments, the analysis can predict the analyte concentration error introduced by the instrument factors over the expected variation range for the apparatus.
As described above, transmission measurements in the “water region” of wavelengths can be used to determine the blood's water content without considering other blood constituents. Once the water content is known, in certain embodiments, the water contribution at each of the wavelengths outside the water region can be calculated and removed. As described above, a water reference spectrum can be fitted to approximate the blood spectrum in a wavelength range of approximately 4.7 microns to approximately 5.3 microns. The fitted water spectrum can then be subtracted from the blood spectrum to produce an effectively water-free spectrum.
In certain transmission measurement systems, the filters have finite width and shape, the cuvettes may or may not be parallel, and the temperatures of the blood and filters may not be controlled. These factors will cause transmission changes that are not due to blood component changes or path length changes. If they are not corrected, the analysis can have corresponding errors in the calculated analyte concentration (e.g., glucose errors). While each of these instrument factors in isolation can result in a corresponding glucose error, in actual systems, the glucose error will be due to a combination of all the instrument factors.
In certain embodiments, the analysis described above can be used to estimate the magnitude of the glucose error for each instrument factor. The analysis can predict the optical density as a function of cuvette shape, filter shape, water temperature and filter temperature for a water-filled cuvette. The glucose error can be evaluated using four wavelengths, two in the water region, one at a glucose reference wavelength (e.g., 8.45 microns) and one at the peak of the glucose absorption (e.g., 9.65 microns). The effects of each instrument factor can be studied separately.
In certain embodiments, a method of evaluating the glucose error comprises calculating the transmission and optical density (od1,od2,od3,od4) at each wavelength for a water-filled cuvette with instrument factor under study. The method further comprises using the optical density of the two water measurements (od1, od2) to determine the water content at the glucose reference and measurement wavelengths (λ3,λ4). The method further comprises calculating the expected optical density (OD3c, OD4c) at the glucose reference and measurement wavelengths. The method further comprises calculating residuals (ΔOD3, ΔOD4), which are the difference between the exact and calculated optical densities at the glucose reference and measurement wavelengths. The method further comprises determining the glucose error by calculating the glucose concentration consistent with residual difference (ΔOD4−ΔOD3).
The optical density corresponding to transmission through a filter for a water-filled non-parallel cuvette with parallel illumination (e.g., exposed to a substantially cylindrical energy beam) can be expressed by the following relation:
where
The water absorption adjusted for water and filter temperature can be expressed by the following relation:
αn(λ)=αo(λ)+β(λ)αTw+γn(λ)ΔTf+ξn(λ)ΔTwΔTf.
An approximate solution for the optical density can be expressed by the following relations:
ODn=αondavg+ΔODn, and
where davg=average cuvette path length and d(x)=davgA=0. In these equations, four instrument factors which contribute to the optical density are specified by the following parameters:
1. Calculation of the Analyte Contribution Errors
Considering each instrument factor separately, ΔODn becomes a function only of that factor. This allows the calculation of the glucose sensitivity for each factor and the evaluation of the accuracy of the approximate solution for the optical density as compared to the exact optical density. Table 2 shows the values of each of the four instrument factors for various simulations. Each row shows the values of the instrument factors for a particular simulation and the corresponding value of ΔODn. The filter shape δ(λn) is a delta function representing an infinitely narrow filter at δn.
Each simulation starts by calculating the set of exact optical densities [od1, od2, od3, od4] using the relation for the exact optical density and the instrument factors from Table 2. For all simulations, the calibration constants are the set [α01
,
α02
,
α03
,
α04
], and the approximate optical densities ODn=
αon
davg+ΔODn.
For the uncorrected case, the calculated path length (dc) can be expressed using the exact optical densities from the water region and the calibration constants in the following relation:
The second two calibration constants can be used to predict the optical densities at (λ3, λ4) as follows:
OD3c=αo3·dc, and
OD4c=αo4·dc.
The residuals can be expressed by the following relations:
ΔOD3=OD3c−od3, and
ΔOD4=OD4c−od4.
The glucose error can be expressed by the following relation:
where (Δg3, Δg4) represents the glucose absorption at (λ3, λ4).
The glucose error for the corrected case can be determined by making the following transformation:
odn→odn−ΔODn,
and repeating the steps outlined above. The corrected glucose error is a measure of how accurately the approximate optical densities equal the exact optical densities. It is an indication of the range over which the instrument parameter (in this case filter width) can vary and still be predicted by the approximate equation.
In certain embodiments, the cuvette/sample chamber shape can be modeled by introducing a curvature (Δc) and wedge (Δp) to a parallel cuvette/sample chamber having a path length (d0). The curvature can be modeled as being on one side of the cuvette, but the sensitivity is the same as if the same curvature is distributed between the top and bottom surfaces. The cuvette width is 2w. Other cuvette shapes may also be modeled.
Graphs of the uncorrected and corrected glucose error as a function of cuvette shape parameters, path length, water temperature variation from nominal, and filter temperature from nominal can be generated using the method described above. The relative contributions of the various cuvette shape parameters can be compared to determine which parameters have the larger effect on the resultant glucose error. This analysis can demonstrate which sensitivities provide glucose errors which are too large unless corrected for. This analysis underestimates the corrected errors since it does not include cross terms when two or more factors are present. This analysis can also show whether the approximate optical density expansion agrees with the exact integral solution, that is, whether the higher order terms are needed.
Further information can be found in U.S. Patent Application Publication No. 2003/0090649, published May 15, 2003, entitled “REAGENT-LESS WHOLE BLOOD GLUCOSE METER,” U.S. Patent Application Publication No. 2003/0178569, published Sep. 25, 2003, entitled “PATHLENGTH-INDEPENDENT METHODS FOR OPTICALLY DETERMINING MATERIAL COMPOSITION,” U.S. Pat. No. 6,862,534, issued Mar. 1, 2005, entitled “METHOD OF DETERMINING AN ANALYTE CONCENTRATION IN A SAMPLE FROM AN ABSORPTION SPECTRUM,” and U.S. Patent Application Publication No. 2005/0036147, published Feb. 17, 2005, entitled “METHOD OF DETERMINING ANALYTE CONCENTRATION IN A SAMPLE USING INFRARED TRANSMISSION DATA.” The entire contents of the above-listed patent and publications are incorporated by reference herein and are made a part of this specification.
V. Vent Configuration for Sample Element
The sample element 800 comprises a first sample chamber 802 and a second sample chamber 804. Each of the sample chambers 802, 804 is configured to hold a material sample which may be drawn from a patient, for analysis by the detection system with which the sample element 800 is employed. Alternatively, the sample chamber(s) 802, 804 may be employed to hold other organic or inorganic materials for such analysis.
In the embodiment illustrated in
In various embodiments, the material that makes up the window(s) of the sample element 800 is completely transmissive, i.e., it does not absorb any of the electromagnetic radiation from the source 20 and first and second filters 40, 60 that is incident upon it. In another embodiment, the material of the window(s) has some absorption in the electromagnetic range of interest, but its absorption is negligible. In yet another embodiment, the absorption of the material of the window(s) is not negligible, but it is stable for a relatively long period of time. In another embodiment, the absorption of the window(s) is stable for only a relatively short period of time, but the analyte detection system 10 is configured to observe the absorption of the material and eliminate it from the analyte measurement before the material properties can change measurably. Materials suitable for forming the window(s) of the sample element 800 include barium fluoride, silicon, polypropylene, polyethylene, or any polymer with suitable transmissivity (i.e., transmittance per unit thickness) in the relevant wavelength(s). Where the window(s) are formed from a polymer, the selected polymer can be isotactic, atactic or syndiotactic in structure, so as to enhance the flow of the sample between the window(s). One type of polyethylene suitable for constructing the sample element 800, and/or the window(s) thereof, is type 220, as extruded, available from KUBE Ltd. of Staefa, Switzerland.
In one embodiment, the sample element 800 is configured to allow sufficient transmission of electromagnetic energy having a wavelength of between about 4 μm and about 10.5 μm through the window(s) thereof. However, the sample element 800 can be configured to allow transmission of wavelengths in any spectral range emitted by the energy source 20.
The sample element 800 may further comprise a first supply passage 806 extending from the first sample chamber 802 to a supply opening 808 and a second supply passage 810 extending from the first sample chamber 802 to the second sample chamber 804. A vent passage 812 may extend from the second sample chamber 804 to a vent opening 814. In the depicted embodiment, both of the first supply passage 806 and the second supply passage 810 extend generally along a supply axis A-A. However, in other embodiments only one of the first and second supply passages 806, 810 may extend along the supply axis A-A.
As with the sample element(s) discussed above, a material sample, such as a fluid sample, may be introduced to the supply opening 808, whereupon the material sample will flow through the first supply passage 806 and fill the first sample chamber 802. The material sample may continue to flow through the second supply passage 810, and then fill the second sample chamber 804. As the material sample fills the sample chambers and the supply passages, the advancing material sample displaces the air within the sample element, which is vented via the vent passage 812 and vent opening 814.
In other embodiments of the sample element 800, only one of the sample chambers 802, 804 is employed (the other of the sample chambers 802, 804 being omitted). In such embodiments, the second supply passage 810 may be omitted, and the sample element 800 may comprise the supply opening 808, the first supply passage 806 extending along the supply axis A-A from the supply opening 808 to the first sample chamber 802, and the vent passage 812 extending from the first sample chamber 804 to the vent opening 814.
In the embodiment depicted in
Instead of or in addition to such an “offset” location of the vent opening 814, the vent passage 812 may include one or more bends 820, situated between (i) a first or upstream end 816 of the vent passage 812, where the passage 812 joins the sample chamber 812, and (ii) the second or downstream end 818 of the vent passage 812, where the passage 812 joins the vent opening 814.
In various embodiments, the bend 820 defines an included angle α of less than or equal to about 135 degrees, less than or equal to about 120 degrees, or less than or equal to about 90 degrees. In the depicted embodiment, the angle α is defined between the respective sidewalls of two straight or relatively straight intersecting portions of the vent passage 812. In other embodiments, the angle α may be defined between the respective centerlines of two intersecting portions of the vent passage 812, where such centerlines are straight or relatively straight. In still further embodiments, the bend 820 comprises a lateral bend.
The use of an offset vent opening 814, and/or a vent passage 812 that incorporates one or more bends as discussed above, advantageously reduces the tendency of a sample material to flow down the length of the vent passage 812 and out the vent opening 814.
As seen in FIG. λ4, the first and second sample chambers 802, 804 may be constructed with different optical pathlengths separating the first and second windows 802a, 802b of the first sample chamber 802, and separating the first and second windows 804a, 804b of the second sample chamber 804, as discussed above with regard to the embodiments of
The second layer 832 may be formed entirely of an adhesive that joins the first and third layers 830, 834. In one such embodiment, the second layer 832 is constructed from the adhesive portion of Adhesive Transfer Tape no. 9471LE available from 3M Corporation. In other embodiments, the second layer 832 may be formed from similar materials as the first and third layers, or any other suitable material. In still other embodiments, the second layer 832 may also be formed as a carrier with an adhesive deposited on both sides thereof. The second layer 832 includes voids which at least partially form the sample chambers 802, 804, supply passages 806, 810, supply opening 808, vent passage 812, and vent opening 814.
As depicted in
The sample element 800 may further comprise an optional stiffening layer 840, which may comprise a layer of acrylic, or any other suitable material, to impart a desired level of rigidity to the sample element 800. Preferably, beveled apertures 842, 844 are formed in the stiffening layer 840 to prevent any absorption of, or other interference with, the electromagnetic radiation passed into or through the sample chambers 802, 804. Other openings may be formed in the stiffening layer 840, as may be appropriate to permit fluid communication with the supply opening 808 and vent opening 814.
Each of the sample chambers 802, 804 is preferably sized to receive a material sample S having a volume less than or equal to about 3 μL (or less than or equal to about 2 μL, or less than or equal to about 1 μL) and more preferably a material sample S having a volume less than or equal to about 0.85 μL. Of course, the volume of the sample chambers 802, 804 can vary, depending on many variables, such as the size and sensitivity of the sample detector 150, the intensity of the radiation emitted by the energy source 20, the expected flow properties of the sample, and whether flow enhancers are incorporated into the sample element 120. The transport of fluid to the sample chambers 802, 804 is achieved preferably through capillary action, but may also be achieved through wicking or vacuum action, or a combination of wicking, capillary action, and/or vacuum action.
One or both of the sample chambers 802, 804 may comprise a reagentless chamber. In other words, the internal volume of the sample chamber(s) 802, 804 and/or the wall(s) 802a-802d, 804a-804d defining the chamber(s) 802, 804 are preferably inert with respect to the sample (e.g., human blood, human blood plasma, or, more generally, human blood components or derivatives) to be drawn into the chamber for analysis. Alternatively, the sample chamber(s) 802, 804 may contain one or more reagents to facilitate use of the sample element in sample assay techniques which involve reaction of the sample with a reagent.
The sample element 800 may also include the optional features of a grip hole 870 and index notches 872, where appropriate to facilitate use of the sample element 800 with an analyte detection system. The grip hole 870 may be employed by the detection system to grip and move the sample element 800 within the analyte detection system. The index notches 872 may be used to determine the relative position of the sample element 800 within the system, and/or to provide an indication of which sample chamber is positioned for analysis by the detection system.
In various embodiments, the vent opening 814 and/or upstream end 816 of the sample element of
The sample element 900 also comprises a vent passage 912 which extends from the sample chamber 902 to a vent opening 914, to place the chamber 902 in fluid communication with the vent opening 914. The vent passage 912 intersects at its upstream end 916 with the sample chamber 902, and a vent axis B-B is defined by the center of the upstream end 916 and the center of the vent opening 914. The vent passage 912 forms a number of transverse sections 950 which extend across the vent axis B-B. As depicted, the transverse sections 950 are interconnected by rounded bends 952 to provide a generally sinusoidal configuration for the vent passage. Other configurations may be employed, however, for the vent passage 912, such as a sawtooth or “square-wave” configuration. In still other embodiments, the vent passage 912 may comprise a plurality of transverse sections 950 interconnected by a number of bends (to form, if desired, a generally sinusoidal, sawtooth or square-wave configuration), and some or all of the transverse sections 950 may (but need not) cross the vent axis B-B.
The vent passage 912 employed in certain of the embodiments depicted in
In the embodiment depicted in
Although invention(s) have been disclosed in the context of certain preferred embodiments and examples, it will be understood by those skilled in the art that the invention(s) extend beyond the specifically disclosed embodiments to other alternative embodiments and/or uses of the invention(s) and obvious modifications and equivalents thereof. Thus, it is intended that the scope of the disclosed invention(s) should not be limited by the particular embodiments described above, but should be determined only by a fair reading of the claims that follow.
This application claims the benefit under 35 U.S.C. § 119(e) of U.S. Provisional Application No. 60/569,331, filed May 7, 2004, titled VENT CONFIGURATION FOR SAMPLE ELEMENT. The entire contents of the above-mentioned provisional application are hereby incorporated by reference herein and made a part of this specification.
| Number | Date | Country | |
|---|---|---|---|
| 60569331 | May 2004 | US |
