METHOD OF PHOTOMETRIC IN VITRO DETERMINATION OF THE CONTENT OF AN ANALYTE IN A SAMPLE

Abstract: The present method is a method of photometric in vitro determination of the content of an analyte in a sample. The sample is located in a measuring chamber device with a measuring chamber, which has a defined radiation path length and has at least one at least partially transparent wall part. The measuring chamber is in optical communication with an optical system adapted for the analyte and comprising a radiation source and a radiation detector. Further, the measuring chamber is adjustable in shape thereby controlling the setting of the radiation path length across the measuring chamber. In a first measuring step a first radiation path length across the measuring chamber is set and radiation at at least one wavelength is transmitted from the radiation source through the measuring chamber and to the radiation detector. Then in a second step the measuring chamber is adjusted in shape thereby setting a second wavelength across the measuring chamber. Radiation at the same wavelength as during the first step is again transmitted from the radiation source through the measuring chamber and to the radiation detector. The analyte content is then determined on the basis of radiation detected in each of the measuring steps.

Description: METHOD OF PHOTOMETRIC IN VITRO DETERMINATION OP THE CONTENT OF AN ANALYTE IN A SAMPLE The present invention relates to a method of photomet- ric in vitro determination of the content of an analyte in a sample located in a measuring chamber device with a measuring chamber which has a defined radiation path length and has one at least partially transparent wall part, said measuring chamber being in optical communi- cation with an optical system adapted for the analyte and comprising a radiation source and a radiation detector. In photometric analysis of the analyte content in a sample located in a measuring chamber, it is in certain cases desired, for example in connection with blood measurements, to make the measuring chamber wall parts located in the radiation transmission path very thin. This may for example be required if the wall parts of a measuring chamber are made from a material significant¬ ly absorbing the measuring radiation. In certain in¬ stances the thin wall parts may, however, give rise to errors in the determination of the analyte content. E.g. this situation will arise when the radiation- wavelength is comparable to the optical thickness of the measuring chamber walls, said optical thickness being defined as the physical thickness of the walls multiplied by the refraction coefficient of the wall material. Thus, the problem is mainly connected with long wave measuring radiation such as infrared or near- infrared radiation. When the measuring chamber wall has smooth, piano- parallel surfaces, radiation will be reflected and/or refracted in the interfaces between the surroundings and the external walls of the measuring chamber and in the interfaces between the internal walls of the mea¬ suring chamber and the sample, respectively. The extent to which the radiation is reflected and/or refracted depends on the refraction coefficients for the wall material, the surroundings and the sample. Said re¬ flected and/or refracted radiation gives rise to a sinusoidal interference spectrum which superposes the measuring spectrum. Particularly in cases where absorp- tion caused by the analyte is relatively small, the above interference spectrum may dominate the measuring spectrum. The interference spectrum is extremely dependent on the thickness of the walls, and even small variation in thickness will displace the spectrum considerably. Such small variation is almost impossible to avoid in auto¬ mated mass-production without extremely great expense. Therefore, each measuring chamber device will have its own characteristic interference spectrum. The effect of interference in connection with foils is disclosed in Hu mel/Schou, "Atlas der Kunststoff-Ana¬ lyse", 1968, ps. 64-65. In this reference a possible solution to the problem is also given; namely to pro¬ vide one of the parallel sides with a fine roughness in order that the reflected radiation beams do not inter¬ fere, but are being scattered diffusely. However, this method is not very advantageous when a large number of uniform products are to be produced as the roughness must be very fine in order to remove interference completely. The roughening of the foil will result in an additional expensive manufacturing process step and further it is difficult to ensure that all products be provided with the same roughness and thereby with the same radiation transmission properties. The object of the invention is to provide a method by which the problems mentioned in respect of photometric analysis of a sample located in a measuring chamber are eliminated. This is achieved by the method according to the inven- tion, said method being characterized in using a mea¬ suring chamber which is adjustable in shape, the ad^ justment in shape controlling the setting of the radia¬ tion path length across the measuring chamber, setting in a first measuring step a first radiation path length across the measuring chamber, transmitting radiation at at least one wavelength from the radiation source through the measuring chamber and to the radiation detector, subsequently setting in a second measuring step a second radiation path length across the measur- ing chamber by adjusting the shape of the measuring chamber, transmitting radiation at the same wavelength as during the first measuring step from the radiation source through the measuring chamber and to the radia¬ tion detector, and determining the analyte content on the basis of radiation detected in each of the measur¬ ing steps. In the present context, the term "photometric determi¬ nation" includes any determination based on measuring of changes in electromagnetic radiation, which under controlled conditions is emitted, transmitted, absorbed or reflected. A general description of photometric determination and optical analyzers is disclosed in "Fundamentals of Analytical Chemistry", Skoog, D.A. & West, D.M., chapter 20, ps. 501-524. Setting the first radiation path length may consist in letting the radiation path length across the measuring chamber equal the initial path length, i.e. the path length of the measuring chamber in its original unad- justed shape or in establishing another path length by adjusting the shape of the measuring chamber. One of the two radiation path lengths may be set to zero so that all of the sample is drained from the radiation transmission path in the measuring chamber. Radiation detected at this radiation path length repre¬ sents absorption and interference from the optical system and the measuring chamber only. Measuring the sample is performed at the other radiation path length, which must not be zero. Radiation transmitted from the radiation source may be wide-band radiation as well as monochromatic radiation and may belong to the ultraviolet range, the visible range, the near-infrared range and/or the infrared range. The radiation source may comprise one single component or several components transmitting radiation at their respective particular wavelength ranges. The radiation detector may also comprise one single component detecting radiation in a particular wave¬ length range or several components detecting radiation in their respective particular wavelength ranges. In case that the radiation source comprises several compo- nents, said components may be integrated in a unit or comprise several physically separated units. The same applies to the radiation detector. The method according to the invention is, as mentioned above, particularly advantageous when the wavelength of the measuring radiation is comparable to the optical thickness of one or more wall parts in the measuring chamber. It has been found that a ratio between the optical thickness and the measuring wavelength above approx. 50 usually lies beyond the range in which unacceptable interference takes place. The measuring chamber device may be provided in several embodiments. One embodiment may comprise a measuring chamber block provided as a fixed component of an analyzer, said measuring block having a measuring chamber for measuring consecutively on a large number of samples. Another embodiment may comprise a single- use device insertable in an optical analyzer adapted for the particular measuring chamber device. An analysis system with a single-use device of the type mentioned above is for example disclosed in Applicant's International Patent Application WO 90/07106. This application discloses a method and a system for photo¬ metric in vitro determination of a blood gas parameter in a blood sample. The blood sample is transferred directly from a patient to a measuring chamber in a sample container, which subsequently is brought into optical communication with an optical system. Measure¬ ment of the blood gas parameter, i.e. C0 2 is performed by transmitting radiation through the sample located in the measuring chamber having a fixed radiation path length. Applicant's International Patent Application WO 90/07109 discloses a method and an analyzer for photo¬ metric in vitro determination of the content of an analyte in a sample of whole blood. The sample is transferred from the patient directly to a measuring chamber comprising a transparent body, the radiation transmission characteristics of said transparent body depending on the concentration of the particular ana¬ lyte in the sample. After filling the measuring cha - ber, the transparent body is equilibrated with the sample whereafter the measuring chamber is deformed in a controlled manner draining the part of the measuring chamber located in the radiation transmission path for sample. The analyte content is then determined on the basis of detection of radiation transmitted through the measuring chamber and the transparent body. None of the measurements are performed directly on the sample in this system due to the fact that the sample has been drained from the radiation transmission path before a measurement is performed. In a preferred embodiment of the present invention a measuring chamber is used wherein the optical transmis¬ sion characteristics of the wall parts located in the radiation transmission path are essentially independent of the adjustment of the measuring chamber. Due to the fact that the measuring chamber wall parts located in the radiation transmission path do not. change their optical transmission characteristics when the shape of the measuring chamber is adjusted, the interference spectrum produced at the surfaces of the wall parts is similar at the two radiation path lengths across the measuring chamber. Thus, by comparing the measurement results from the two different radiation path lengths, the contribution from the interference spectrum may be removed completely in the determination of the analyte content. In another preferred embodiment of the invention a measuring chamber is used comprising two opposite at least partially transparent wall parts located in the radiation transmission path. In a further embodiment of the invention a measuring chamber is used comprising one at least partially transparent wall part and one opposite wall part re¬ flecting incoming radiation, said wall parts being located in the radiation transmission path as well. In a preferred embodiment the adjustment in shape of the.measuring chamber is provided by displacement of at least one of the measuring chamber wall parts located in the radiation transmission path. The content of a particular analyte in a sample is calculated on the basis of measurements of the trans¬ mission properties of the sample at at least one wave- length, which must fall within a range where the par¬ ticular analyte absorbs. In photometric determination of an analyte in a sample, in which the solvent is strongly absorbing at the measuring wavelength, it is usually attempted to make the radiation path length through the sample very short in order to reduce loss of energy, generation of heat in the sample, etc. The setting of a short radiation path length makes, however, heavy demands on the roe- chanical accuracy of the analyzer and even minor inac¬ curacies in the radiation path length may have a deci¬ sive influence on the measuring result. The problem may be overcome by determining the radiation path length in each measurement. In a preferred embodiment of the invention radiation at a wavelength additional to the at least one wavelength is transmitted from the radiation source through the measuring chamber and to the radiation detector and the difference between the first and second radiation path lengths is determined on the basis of the radiation detected at each of the wavelengths in each of the measuring steps. The difference between the first and second radiation path lengths equals the effective radiation path length through the sample as described more closely in the detailed part of the specification. In an embodiment of the method according to the inven¬ tion the content of one additional analyte in the sample may be determined simultaneously with the first analyte by including radiation at one additional wave¬ length in the measuring steps. This additional wave¬ length must be a wavelength where said one additional analyte absorbs. Correspondingly, a number of addition- al analytes may be determined by including a number of additional wavelengths at least equal to the number of additional analytes. The method according to the invention is especially useful in connection with analytes which at the measur¬ ing wavelength absorb weakly compared to the solvent, the analyzer and/or the measuring chamber. In this case the measuring spectrum relating to the analyte will to a considerable degree be superposed by the interference spectrum of these other constituents or parts. In a preferred embodiment of the invention the C0 2 content in a sample is determined on the basis of an examination of the transmission characteristics of the sample for radiation at wavelengths at approx. 4228 nm. 4268 run and 4308 nm. Determination of the C0 2 content by irradiating with radiation at said wavelengths is disclosed in i.a. Applicant's above-mentioned Interna¬ tional Patent Application WO 90/07106. In the specifi- cation of US Patent US 4509522, Manuccia et al. a photometric method for in vivo determination of the content of blood gases in blood is disclosed; i.a. C0 2 is determined by irradiating with radiation at approx. 4.2 μm. The basic principles for determining C0 2 by transmission measurement at a wavelength of approx. 4.2 μm is disclosed in the specification of British Patent Application GB 2160646, Mosse, CA. & Hillson, P.J. and in the specification of European Patent Application EP 253559, Nestor, J.R. The content of said publications is considered incorporated into the present application by reference to the publications. The invention further relates to an analyzer for use in the method according to the invention, said analyzer comprising a radiation source, a radiation detector and a measuring chamber device with a measuring chamber, said measuring chamber having at least one at least partially transparent wall part and being in optical communication with the radiation source and the radia- tion detector, and being characterized in that the measuring chamber is adjustable in shape, that the analyzer is provided with means which are adapted to adjust the measuring chamber in shape in a controlled manner and which when activated set first and second radiation path lengths, respectively, across the mea¬ suring chamber, and that the radiation source is adapt¬ ed to transmit radiation at at least one wavelength through the measuring chamber to the radiation detector at the respective first and second radiation path lengths. Preferably, the analyzer according to the invention comprises means for converting the radiation detected and means for processing the converted radiation data in order to derive the content of the analyte in the sample. Alternatively, the data processing means may be comprised in a separate data processing unit σonnect- able to the analyzer. Further it is preferred that the analyzer comprises means for displaying the analyte content. Alternative¬ ly, the analyzer is adapted for connection to display means, such as for example a data screen, a display, a printer or a plotter. The invention further relates to a measuring chamber device with a measuring chamber for use in an analyzer according to the invention, said measuring chamber device being characterized in that the measuring cham¬ ber is adjustable in shape in a controlled manner setting first and second radiation path lengths across the measuring chamber. In a preferred embodiment of the measuring chamber device the optical transmission characteristics of the measuring chamber wall parts adapted to be placed in the radiation transmission path are essentially inde¬ pendent of the adjustment in shape of the measuring chamber. Preferably, the measuring chamber comprises two oppo¬ site at least partially transparent wall parts, but it may comprise one at least partially transparent wall part and one opposite wall part reflecting incoming radiation. The measuring chamber device may include one single measuring chamber or several measuring chambers ar¬ ranged in series or in parallel. Preferably, the mea¬ suring chamber device is made from an injection mould- able polymeric base material. A suitable base material is polyethylene terephthalate (PETP) , which for example is sold under the tradename ARNITE™ from AKZO, Arnhem, Holland. The partially transparent wall parts and the measuring chamber device proper may differ in material. The wall material is primarily selected on the basis of its transmission properties at the measuring wavelengths and its applicability in the manufacturing process of the entire measuring chamber device. When using a measuring chamber device in the form of a single-use component, the optical communication between the radiation source, the radiation detector, and the measuring chamber device may be established by placing the measuring chamber device in a particular station in the analyzer. Alternatively, the optical communication may be established by means of one or several optical fiber cables connecting contact elements on the measur- ing chamber device to the analyzer. The invention will now be further explained in the following with reference to the drawing and the subse¬ quent examples. In the drawing: Figs, la and b show perspective views of a measuring chamber device for use in the method according to the invention; Fig. lc shows a sectional view on an enlarged scale along the line I-I in Fig. la; Fig. 2 shows interference obtained by transmitting radiation towards a thin foil with two piano-parallel surfaces; Fig. 3 shows an absorption spectrum for a 23 μm foil of polyethylene terephthalate (PETP) ; Fig. 4 shows a partial cross section of an optical unit in an analyzer according to the invention and a measur¬ ing chamber device according to the invention for photometric determination of an analyte in a sample with a schematic representation of the components of the optical unit; Figs. 5a and b show partial cross sections of a measur¬ ing chamber device according to the invention and of the parts of an optical unit in an analyzer according to the invention between which the measuring chamber device is secured when measuring, the measuring chamber device and the securing parts being shown in two dif¬ ferent positions in relation to each other; Fig. 6 shows an absorption spectrum for water having a C0 2 content of approx. 100 mmHg; Fig. 7 shows an absorption spectrum for whole blood adjusted to a C0 2 content of approx. 419 mmHg by to- nometry; and Fig. 8 shows a view of a preferred embodiment of a measuring chamber device according to the invention for use in determination of the C0 2 content in a sample of whole blood. In the different figures same parts are provided with identical reference numerals. Figs, la and b show an embodiment of a measuring cham¬ ber device for use in determination of an analyte in a sample. The measuring chamber device, generally desig- nated 4000, is part of an analyzer having an optical unit as further described below in connection with Eig. 4. The measuring chamber device 4000 consists of two identical halves 4001 and 4002. Said halves are made by means of injection moulding of a transparent "soft" plastic material, for example polyethylene terephthala¬ te (PETP) of the type ARNITE™ from AKZO, Arnhem, Hol¬ land. The two halves are assembled by pins 4005 and 4006 in the half 4001 engaging mating, not shown re¬ cesses in the half 4002, while not shown pins in the latter engage recesses 4007 and 4008 in the half 4001. Thereafter, the two halves are welded together by means of ultrasonic welding. The line of material 4009 outlined in the half 4001 shown in the figure as the lower half forms a welding seam after the welding. Said line of material lies along the edge of a longitudinal open conduit 4010, which centrally expands transversely and forms a mea¬ suring chamber 4011 with a through hole 4012 directed perpendicular to the conduit 4010. The through hole 4012 is covered by a window 4004 made from a 23 μm foil of polyethylene terephthalate (PETP) of the type Meli- nex S from ICI, Cheshire, England. The corresponding through hole in the half 4002 is covered by a similar window 4003. The windows 4003 and 4004 are mounted in the halves 4001 and 4002 prior to assembly. The mounting of the window 4004 is carried out by said 23 μm PETP foil being stretched across the through hole 4012 in the half 4001 whereafter the foil by means of an ultrasonic welding head is welded to the half 4001 in a border area 4013 next to the through hole 4012. The excessive foil is then punched by means of a perforating punch leaving only the fixedly welded window 4004. By stretching the foil across the hole 4012 it is ensured that the window 4004 is plane after the ultrasonic welding. The window 4003 is affixed to the cuvette half 4002 in a similar manner. The windows 4003 and 4004 are elastically displaceable in a direction perpendicular to the conduit 4010. Fig. lc, which is a view along the line I-I of Fig. la, shows the central part of the measuring chamber device 4000 with the measuring chamber 4011 delimited by the windows 4003 and 4004. In Fig. 2 is shown a section of a foil f with a refrac¬ tion coefficient n 0 and provided with piano-parallel, smooth surfaces s t and s 2 . A radiation beam i 0 with a particular measuring wavelength is transmitted towards the surface s t . Assuming that the incoming radiation i 0 has an angle of incidence less than the critical angle for total reflection, the incoming radiation will, when falling onto the external, smooth surface s, of the foil f , split into a reflected beam r, and a transmit¬ ted beam j depending on the refraction coefficients n j and n 2 of the adjacent materials. The transmitted beam t.χ will, when falling onto the internal, smooth foil surface s 2 , split into a transmitted t u and a reflected t lr beam, which again will split into a reflected t 2 and a transmitted r 2 beam. When the optical thickness of the foil f is comparable to the wavelength i 0 of the incoming radiation, the re¬ flected beams r,, r 2 , r 3 ... will interfere constructive¬ ly or destructively dependent on the phase differences. This applies to the transmitted beams too. The inter¬ ference gives rise to a sinusoidal interference spec- trum, which influence the transmission spectrum of the foil. The following relation applies between the thick¬ ness d of the foil and the interference spectrum ob¬ tained at the piano-parallel surfaces s s 2 : where d is the thickness of the foil; n 0 is the refraction coefficient of the foil; λ_, λ b are wavelengths in the interference spectrum; and λ b -λ„ is a wavelength interval corresponding to one period in the interference spectrum. As seen from (1) , a change in the thickness of the foil d will cause a displacement of λ, in relation to λ b and consequently a change of the period of the interference spectrum. As it is impossible in practice to make the foil windows 4003 and 4004 in a series of measuring chamber devices 4000 completely identical in thickness each measuring chamber device will have a characteris¬ tic interference spectrum from the foil windows. This means that the analyzer cannot be set in advance to compensate for the interference spectrum. Fig. 3 shows an absorption spectrum in the wavelength range 2500-5000 nm for a 23 μm foil of PETP correspond¬ ing to the foil used for the windows 4003 and 4004 in the measuring chamber 4011 of the measuring chamber device. The spectrum is recorded on a spectrophotometer of the type 157 from PERKIN-ELMER. As seen from the figure, the foil is relatively transparent to radiation in the range mentioned, as approx. 80% of the transmit¬ ted radiation is transmitted through the foil when the special absorption bands relating to the material PETP are disregarded (for example at a wavelength of approx. 3380 nm) . Moreover, it is seen from Fig. 3 that the spectrum for the material is superposed by an apparent¬ ly sinusoidal interference spectrum. The superposed spectrum results from interference of radiation re¬ fracted/reflected on the smooth surfaces of the foil, cf. the above description of Fig. 2. Fig. 4 shows a prototype of an optical unit 400 for use in the determination of an analyte in a sample. The sample is located in the measuring chamber device 4000, which is secured between a movable part 410 and a stationary part 412. The movable part 410 may be dis¬ placed along the centre line cl by means of an electro- magnet 411. The optical unit 400 comprises a radiation source 401 _n the form of a thermal radiation unit, more specifically a CrNi filament heated to a tempera¬ ture of approx. 1050°C. The radiation source 401 is specially made for the present purpose by Applicant. The optical unit 400 further comprises a reference diode 413 of the type SFH 225 from Siemens, Munich, Germany, which regulates the radiation of the filament 401. Radiation from the radiation source 401 is transmitted to a parabolic mirror 402 (0 10 mm, f = 3 mm) specially made for the present purpose by Applicant. The parabol¬ ic mirror 402 transmits the radiation from the filament 401 through a band-pass filter 403 (center value 4240 nm, half band width 200 nm) from Spektrogon, Taby, Sweden, and from there through the blood sample in the measuring chamber device 4000. From the measuring chamber device 4000, the radiation is transmitted through a slit 404 (0.5 x 3 mm) located on a sapphire window (0 3 x 0.4 mm), past a chopper 408, which by means of a DC motor 409 provides a chopper frequency of approx. 800 Hz. After passage of the chopper 408, the radiation falls onto an off-axis parabolic mirror 405 (f = 65 mm) specially made by Applicant which reflects the radiation as a parallel pencil onto a grating 406 (a 300-lines grating optimized to approx. 4.3 μm) from Optometrics, Leeds, England. The grating 406 deflects the radiation back onto the parabolic mirror 405, which focuses the radiation onto a detector 407 from Hamamatsu, Hamamatsu City, Japan. The detector 407 comprises a diode array consisting of three PbSe-diodes (0.5 x 2 mm, center distance 1 mm) built-into a T05- housing with a band-pass filter (center value 4400 nm, half band width 650 nm) . The diodes in the diode array 407 register the intensity of radiation at their re¬ spective of the three measuring wavelengths, which are separated by means of the grating 406 and the off-axis parabolic mirror 405. From the diodes electric signals representing the intensity of radiation incoming to the diodes are sent to a analog/digital converter (not shown) and from there to a data processing unit (not shown) performing the calculations of the content of C0 2 in the sample on the basis of the signals received. Figs. 5a and b show a partial section corresponding to Fig. lc through a measuring chamber device 4000 accord¬ ing to the invention placed between the movable part 410 and the stationary part 412 of an optical unit for measuring of the C0 2 content in a sample. As described in connection with Fig. 4 measuring radiation is trans¬ mitted through a band-pass filter 403 in the movable part 410, through the measuring chamber device 4000 to the slit 404 in the stationary part 412. When a measuring chamber device 4000 is arranged in the analyzer, the movable part 410 of the optical unit is displaced towards one of the windows 4003 of the mea¬ suring chamber device and pushes the measuring chamber device 4000 and the opposite window 4004 towards the stationary part 412 of the optical unit. The measuring chamber device 4000 is now secured in the optical unit with one window 4003 adjacent to the movable part 410 and the second window 4004 adjacent to the stationary part 412. By displacing the movable part 410 into several predetermined positions, the windows 4003 and 4004 are displaced transversely to the measuring cham¬ ber 4011 and the measuring conduit 4010 thereby varying the distance between the windows in a predetermined manner. This adjustment in shape of the measuring chamber 4011 results in setting the radiation path length across the measuring chamber. In the position shown in Fig. 5a the movable part 410 of the optical unit is displaced to a first position, and the distance between the windows 4003 and 4004 of the measuring chamber device 4000 defines a first radiation path length across the measuring chamber corresponding to for example 100 μm. In Fig. 5b the movable part 410 is displaced to a second position, and a second radiation path length corresponding to for example 50 μm is defined. By giving the movable part 410 and the stationary part 412 of the optical unit the same external shape in the areas getting in contact with the windows 4003 and 4004, a uniform, symmetric displacement of the windows 4003 and 4004 and thus of the measuring chamber 4011 is ensured. As mentioned in connection with Figs, la-c the foil for the windows 4003 and 4004 is stretched during mounting in the halves 4001 and 4002 of the measuring chamber device to ensure plane windows after ultrasonic weld¬ ing. When displacing the windows 4003 and 4004 between the two measuring positions, the thickness of the windows will change. However, this change may be so minimal that its influence on the determination of the analyte may be disregarded. This is clarified by the following example: When a foil window corresponding to the windows 4003 and 4004 is displaced 100 μm from the resting position and from this position is displaced an additional 25 μm, the tension in the window causes an insignificant change of thickness, viz. approx. 12 nm, which is- considerably less than the thickness variations between the windows in mass-produced measuring chamber devices. The thickness change of the window due to the displace¬ ment results in a negligible change in the period of the above described sinusoidal interference spectrum of approx. 0.1 nm. Due to the fact that the thickness change of the windows 4003 and 4004 is negligible during the displacement the interference caused by the windows 4003 and 4004 in the measuring situations shown in Figs. 5a and b may be regarded similar. Fig. 6 shows an absorption spectrum in the wavelength range 3300-6000 nm for water with a content of C0 2 of approx. 100 mmHg and a radiation path length of approx. 100 μm. The spectrum is recorded at an IR spectropho- tometer of the type Beckman IR9. It appears from the figure that a content of C0 2 causes absorption at a wavelength of approx. 4268 nm. However, said absorption is, as seen, small in relation to the absorption caused by the water. Due to the fact that absorption on ac- count of C0 2 is relatively small in relation to absorp¬ tion caused by water interferences caused by, for example the measuring chamber device, the optical system, the surroundings, etc., may have a substantial effect on the measurement result. As seen from Fig. 6, a C0 2 content of approx. 100 mmHg and a radiation path length of approx. 100 μm will cause a change of the transmission of around 3% only. When comparing this with the foil spectrum in Fig. 3, from which it appears that the sinusoidal superposition deriving from inter- ference in the surfaces of the foil causes a variation in the transmission spectrum of around 5%, it appears that the interference spectrum from the foil windows will strongly influence the actual measuring spectrum. Thus, it is necessary to either remove the unwanted interferences or compensate therefor in the calculation of the C0 2 content in the sample. Fig. 7 shows an absorption spectrum for whole blood adjusted to a C0 2 content of approx. 419 mmHg by to- nometry. The spectrum is like the previous one recorded on an IR spectrophotometer of the type Beckman IR9. It appears from this absorption spectrum as well that a content of C0 2 in the sample causes absorption at a wavelength of approx. 4268 nm.- Fig. 8 shows a preferred embodiment of a measuring chamber device 40 according to the invention for deter¬ mination of the C0 2 content in a sample of whole blood. The measuring chamber device 40 is provided as a sam- pling device in which the blood sample is transferred directly from a patient to the measuring chamber de¬ vice. The measuring chamber device 40 comprises a body 41 consisting of two parts which after assembly form an internal continuous sample conduit 44 with a cross sec¬ tion of 0.3 x 2 mm. At the end of the body 41, where the inlet of the conduit is located, the body 41 is provided with a Luer cone 42 and thus adapted to be connected to a needle 43 of the type usually employed for blood sampling. At the end opposite the inlet opening, the conduit 44 is provided with a hydrophil¬ ic/hydrophobic filter 48, and at this end 49 the body 41 is adapted for coupling to a traditional plunger syringe which may serve as an sampling aid in special situations. Around the middle of the conduit 44 it expands while forming a measuring chamber 45 with a diameter of 8.6 mm. At this location each of the two parts of the body 41 comprise a through hole 46a, 46b perpendicular to the conduit 44 and having a diameter of 6.0 mm, said holes facing each other after assembly of the body 41. On the inside of the conduit 44 each of the holes 46a, 46b are covered by a foil window 47a and 47b, respec¬ tively, of a diameter corresponding to the measuring chamber 45 and made from a 23 μm polyethylene tere¬ phthalate foil. Prior to assembly of the body 41 the foil windows 47a, 47b are mounted by means of ultrason- ic welding in a manner as described above in connection with Figs. la-c. Thus, the measuring chamber 45 is delimited transversely to the conduit 44 by the two windows 47a, 47b. The theoretical background of the method according to the invention is described in the following wherein the analyte is exemplified by C0 2 . When transmitting radiation with wavelength λ and intensity I λ in an optical system and through a measur¬ ing chamber having a radiation path length t and mea¬ suring the intensity I, λ of the transmitted radiation, the total absorbance A λ of the optical system and the sample may be determined as: Said absorbance consists of the sum of the absorbances of the various components and may be written as: A iΛ = A (H 2 0)+A λ (C0 2 )+A, ,λ (i b )+A λ (i f )+A λ (i.)+A λ (i 0 ) (3) where λ is the wavelength of the transmitted radia¬ tion; I is the radiation path length across the mea¬ suring chamber; &r , x( H _0) is the absorption caused by water in the sam¬ ple; A fΛ (C0 2 ) is the absorption caused by C0 2 in the sample; A, (i b ) is the absorption caused by other analytes in the sample; A_ .λ (i f ) is tne absorption caused by the windows of the measuring chamber; Af.χ(i.) is the absorption caused by the atmosphere; and A/, λ (io) is the absorption caused by the optical sys¬ tem. The first three terms of (3) depend on the composition of the sample and on the radiation path length across the measuring chamber, whereas the last three terms depend on the measuring chamber device, the optical 10 system, and the atmosphere, but are independent of the sample. When performing two measurement steps at their respec¬ tive radiation path lengths £1, £2 across the measuring 15 chamber (cf. Figs. 5a and b) and using radiation having the radiation intensities I λ>1 and I^ 2 , respectively, the total absorbance A nλ and A t2λ , cf. (3), for each step is obtained. By taking the difference ΔA λ = A nλ - A 2V between said absorbances, the last three terms of (3) 2.0 are left out: ΔA λ = A nΛ - A,2,λ = log (Iχ , ,/I n,λ ) - log (I λ>2 /I f2, χ) = log (Iχ,,/Iχ, 2 ) + log (I, 2, χ/I n , λ ) = A nΛ (H 2 0) - A, 2>λ (H 2 0) + 25 A , λ (C0 2 ) - A, 2Λ (C0 2 ) + When the intensities l Ki and I 2 of the incoming radia¬ tion at the two radiation path lengths £1 and £2 are 30 the same, the calculations are made independent of the intensity as the term log (I λ, ι/I λt2 ) equals zero. Thus, in the calculations it is only necessary to know the intensities of the transmitted radiation I„ λ and I /2λ . According to Lambert-Beer's Law the absorbance A λ re¬ lating to a given analyte at a given wavelength λ is determined as: A λ (C0 2 ) = e λ (C0 2 )-£-C(C0 2 ) (5) where e λ (C0 2 ) is the molecular absorption coefficient for C0 2 at the wavelength λ; £ is the radiation path length through the sample containing C0 2 ; and C(C0 2 ) is the molecular concentration of C0 2 in the sample. By introducing Lambert-Beer's Law (5) in the expression for ΔA λ , cf. (4) the following expression is obtained: = e λ (H 2 0) «(£l-£2) -C(H 2 0) + e λ (C0 2 ) • (£l-£2) -C(C0 2 ) + eχ(i b )-(£l-£2)-C(i b ) = e λ (H 2 0) ' A£ ' C(H 2 0) + e λ (C0 2 ) ΑZ - C(C0 2 ) + e λ (i b ).Δ£-C(i b ) (6) where Δ£ = £1-22 may be considered as the effective radiation path length through the sample. The last term of (6) corresponds to absorption deriving from other analytes in the sample. It has proved allow¬ able to consider said term as deriving from only one analyte, i b , the molar concentration C(i b ) of which then becomes a theoretical value. When measuring on blood, it is usually desired that the content of C0 2 is expressed by its partial pressure. The relationship between the concentration of C0 2 in a fluid sample and the partial pressure of C0 2 in the sample may be written as: C(C0 2 ) = α t (C0 2 )-pC0 2 (7) where α t (C0 2 ) is the solubility coefficient for C0 2 in the sample at the temperature t; and pC0 2 is the partial pressure of C0 2 in the sample. When introducing (7) into the second term of (6) the following expression is obtained: ΔA λ = e λ (H 2 0) •Δ_-*C(H 2 0) + e λ (C0 2 ) 'α t (C0 2 ) »Δ£«pC0 2 + e λ (i b )-Δ£-C(i b ) = e λ ' (H 2 0) -Δ£+e λ ' (C0 2 ) .Δ£-pC0 2 +e λ (i b ) -Δ£-C(i b ) = € λ ' (H 2 0) .Δ£+€ λ ' (C0 2 ) -C (C0 2 )+e λ (i b ) -C (i b ) (8) where e λ ' (H 2 0) = e λ (H 2 0) «C(H 2 0) ; e λ '(C0 2 ) = e λ (C0 2 )-α t (C0 2 ); C (C0 2 ) = Δ£«pC0 2 ; and C'(i b ) = Δ£-C(i b ) When for each radiation path length £1, £2 measurements are made at three wavelengths λl, λ2, λ3, the following three equations, cf. (8) , may be set up: AA λl = e λl ' (H 2 0) -Δ£ + € M ' (C0 2 ) -C (C0 2 ) + e λl (i b ) -C (i b ) ..Ax, = _χ 2 '(H 2 0)-Δ£ + eλ2 '(C0 2 )-C'(C0 2 ) + eλ2 (i b ) -C (i b ) (9) ΔA 3 = eλ3 '(H 2 0)-Δ£ + e w '(C0 2 ).C'(C0 2 ) + e>e ( i b ) -C (i b ) From said three equations the three unknown quantities Δ£, C (C0 2 ) and C (i b ) may be calculated, and the par- tial pressure of C0 2 in the sample may be determined as: pC0 2 = C (C0 2 )/Δ£ (10) When the method according to the invention is to be performed in practice the absorption coefficient matrix E = (11) is predetermined experimentally by measuring for each of the wavelengths λl, λ2, λ3 samples of particular known compositions. Determination of the absorption coefficient matrix E is illustrated in the following example. A sample-containing measuring chamber device corre- sponding to the one shown in Fig. 8 is inserted into an optical system wherein the radiation path length may be set accurately and thus is known. Radiation is trans¬ mitted from the radiation source through the measuring chamber to the radiation detector. Measurements are performed at the three wavelengths λl = 4228 nm, λ2 = 4268 nm, λ3 = 4308 nm with a band width of approx. 20 nm and at the radiation path lengths £1 = 100 μm and £2 = 50 μm. The intensity of the transmitted radiation at the three wavelengths is kept constant. For each wavelength λl-λ3 measurements are performed on a sample of pure water without C0 2 or other analytes. On the basis of the measured absorption for each wave¬ length, the absorption coefficients relating to water are determined by means of Lambert-Beer's Law, cf. (5) . As absorption deriving from C0 2 at the wavelengths λl = 4228 nm and λ3 = 4308 nm is insignificant compared to C0 2 absorption at the wavelength λ2 = 4268 nm, the absorption coefficients e '(C0 2 ) and e u ' (C0 2 ) are set to 0.0. The absorption coefficient e u ' (C0 2 ) is determined by measuring a sample of water with a known content of C0 2 without other analytes. On the basis of the previ¬ ously determined absorption coefficients for water, the radiation path length across the measuring chamber and the C0 2 content in the sample, e u ' (C0 2 ) may be deter¬ mined. In the determination of the C0 2 content in a sample it is essential to consider the absorption caused by other analytes in the sample (e λ (i b ) «C (i b ) ) - the particular values for e λ (i b ) and C (i b ) are unimportant. As men¬ tioned previously, C (i b ) is only a theoretical value of no real physical importance. Therefore, the determi¬ nation of the absorption coefficients e λl (i b ), e λ2 (i b ) , _χ 3 (i b ) is not a matter of determining these coeffic¬ ients definitely, but determining the ratios among them. The absorption coefficients e λl (i b ), e λ2 (i b ) and £χ 3 (i b ) are determined by measuring at the three measuring wavelengths λl, λ2, λ3 on a sample of whole blood with a known content of water and C0 2 . An equation set cor¬ responding to (9) may be set up. The terms deriving from water and C0 2 may be calculated on the basis of the previously derived absorption coefficients and deducted from the equations. Three equations are left expressing the relation between absorption caused by other analytes at each of the three wavelengths. The relation between these absorbances corresponds to the relation among the absorption coefficients e λ ι(i b ), eχ 2 (ib) and e _j(ib)/ as ' (ib) i the same at the three wavelengths. The smallest of the absorption coefficients is set to 1.0 • 10" 3 μm being of the same magnitude as the absorp¬ tion coefficients for water, and the other coefficients are determined relatively thereto. The absorption coefficient matrix is determined as: e 4228 ' (H g p) e 4228 * ( CO z ) e 4228 (i b ) E = e« 6 β ' H z O) e 4268 ' ( CO z ) e 4268 ( i b ) e 4308 ' (H 2 0) e 4308 ' {C0 2 ) ε 4308 (i b ) ) '10 . 50 MO -3 μm -ι 0 . 0 1. 59 lO -3 11 . 12 MO -3 μjπ "1 2 . 8-10 "6 _πmHg r"1 μ_π "1 1. 37 *10 '3 (12 ) lll .75 .10- 3 μm '1 0 . 0 1. 00 __0 "3 When measuring on a sample of whole blood it is re¬ quired, as mentioned previously, to measure at short radiation path lengths through the sample as the water content in the sample causes relatively large absorp¬ tion. Relevant radiation path lengths for measuring on whole blood fall in a range from about zero to max. 200 μm. However, the radiation path length must not so short that standing waves are produced between the inside of the measuring chamber walls, or in practice no less than approx. 25 μm. In order to improve the measurement results it is preferred to perform the measurement- steps three times. A measurement thus comprises setting the radiation path length initially to approx. 100 μm, then to 50 μm, again to 100 μm, then to 50 μm and again to 100 μm and then 50 μm. At each radiation path length the intensity of the radiation transmitted through the measuring chamber is measured during 5 seconds. On the basis of the "three sets" of absorptions obtained three values for pC0 2 are determined, and the content of C0 2 in the sample is calculated as the mean value. The advantage of the method according to the invention, by which measurements are performed at different radia- tion path lengths compared to a prior art method by which the radiation path length is kept constant, is clearly seen from the following comparative example. Determination of the C0 2 content in gas samples was performed in two experiments. In the method used for the first experiment the radiation path length was kept constant at 65 μm during the entire course of measur¬ ing. In the method used for the second experiment the radiation path length was varied between 50 μm and 100 μm as described above. In each experiment measurements were performed on a set of gases consisting of 3 gases each having a different composition of C0 2 , 0 2 and N 2 . Two not quite identical sets of gases were used, the lack of identity being of no importance in the present context. In Table 1 the compositions of the gases are listed. Index A denotes a gas used for the first experiment and index B denotes a gas used for the second experiment. Table 1 Table 1: The composition of measuring gases. In each set of gases one gas (GAS 2A or 2B) has a content of C0 2 and 0 2 normal for blood. The remaining gases have a composition different from this. One has a larger content of C0 2 and a smaller content of 0 2 (GAS 1A and IB) and the other has a larger content of 0 2 and a smaller content of C0 2 (GAS 3A and 3B) . For each of the gases GAS 1A, IB, 3A and 3B the content of C0 2 in the gas was determined on the basis of five subsequent measurements in the same measuring chamber. The mean value of the five C0 2 determinations and the standard deviations were calculated. In each of the gases GAS 2A and 2B the content of C0 2 in the gas was determined three times by use of three different measuring chambers. Five measurements are performed with each of the three measuring chambers, and the mean values and standard deviations are calcu¬ lated, as described for the gases 1A-3B above. The results from the measurements performed appear in Tables 2 and 3 below, where Table 2 lists the results from the first experiment, and Table 3 lists the re¬ sults from the second experiment. In the tables x is the mean value from five measurements of pC0 2 in the same measuring chamber; and s is the standard deviation. Table 2 Table 2 : Measuring results from the prior art meth¬ od. Table 3 Table 3 : Measuring results from the method according to the invention. When comparing the results from the two experiments (Table 2 and 3) it is clearly seen that measuring according to the invention at two radiation path lengths across the measuring chamber is highly advanta- geous. As appearing from Table 2 the results for GAS 2A are totally unacceptable. The mean values differ very much and the standard deviations obtained for measurements performed in the same measuring chamber are extensive. In the second experiment when measuring on GAS 2B the mean values obtained from the different measuring chambers do not vary much and the standard deviation is reduced considerably. When studying the results from measuring the other gases (GAS 1A, IB, 3A and 3B) , it is also apparent that the method according to the invention is superior to the prior art method. The above-mentioned use of the method may, of course, be used for determination of other analytes than C0 2 , and it is no condition that the solvent is water. For other analytes and/or solvents it is in each particular case required to determine the absorption coefficient matrix, cf. (11) . When the analyzer, by means of which a sample is to be analyzed, is designed in such a manner that the radia¬ tion path length across the measuring chamber may be set accurately, the above-mentioned determination of a given analyte in a sample may be performed by measuring at two wavelengths only. Hereby the equation set on the basis of which the analyte content is determined will include only two equations with two unknown quantities. In the example shown above the solvent (water) is strongly absorbing at the selected measuring wave¬ lengths. In case it is desired to determine the content of an analyte in a sample, in which the solvent does not absorb at the measuring wavelengths, the equation set, cf. (9), for the calculations will also include only two equations. Further, when using an analyzer wherein the radiation path length may be set accurate¬ ly, the equation set will be further reduced. In this case it will be required to measure at one wavelength only and thus the analyte content may be determined from one equation with one unknown quantity. Similarly, the content of more analytes in a sample may be determined by measuring in the same measuring cham¬ ber. In equation (3) the absorbance contribution for the analyte/analytes is incorporated, and measuring is performed at one/several further wavelengths. Accord¬ ingly, an equation set corresponding to (9) may be set up; this equation set contains one or several further equations and unknown quantities depending on how many further analytes are to be determined. To ensure a uniform adjustment of the measuring chamber in a measuring chamber device according to the inven¬ tion, it is preferred that the measuring chamber be symmetrically designed, cf. Figs, la-c and Fig. 8. Moreover, in that case the measuring chamber device need not be oriented in a particular way in relation to the related optical system. The measuring chamber may, if desired, be designed asymmetrically, for example the partially transparent areas may be different in thickness, area size and/or be made from different materials. Further, only one side of the measuring chamber need be adjustable. With this asymmetrical design it is required that the mea¬ suring chamber device be oriented in a particular way in relation to the optical system made especially for this measuring chamber device. Furthermore, the measuring chamber may comprise a par¬ tially transparent wall part on one side of the chamber and an opposite wall part reflecting the radiation. In the corresponding optical system the radiation trans- mission paths for radiation transmitted towards the measuring chamber device and for radiation transmitted from the measuring chamber, respectively, lie on the same side of the measuring chamber device. The measuring chamber device may be made in several other embodiments provided that the measuring chamber is adapted to interact with a corresponding optical system and that the adjustment in shape of the measur¬ ing chamber controls the setting of the radiation-path length across the measuring chamber.

Claims: C L A I M S 1. A method of photometric in vitro determination of the content of an analyte in a sample located in a measuring chamber device with a measuring chamber which has a defined radiation path length and has one at least partially transparent wall part, said measuring chamber being in optical communication with an optical system adapted for the analyte and comprising a radiation source and a radiation de¬ tector, c h a r a c t e r i z e d in using a measuring chamber which is adjustable in shape, the adjustment in shape controlling the setting of the radiation path length across the measuring chamber, setting in a first measuring step a first radiation path length across the measuring chamber, transmitting radiation at at least one wavelength from the radiation source through the measuring chamber and to the radiation detector, subsequently setting in a second measuring step a second radiation path length across the measuring chamber by adjusting the shape of the measuring chamber, transmitting radiation at the same wavelength as during the first measuring step from the radiation source through the measuring chamber and to the radiation detector, and determining the analyte content on the basis of radiation detected in each of the measuring steps. 2. A method according to claim 1, c h a r a c t e r i z e d in that the optical transmission characteristics of the measuring chamber wall parts located in the radiation transmission path are essentially inde¬ pendent of the adjustment of the measuring chamber. 3. A method according to claims 1 or 2, c h a r a c t e r i z e d in that the measuring chamber comprises two opposite at least partially transparent wall parts located in the radiation transmission path. 4. A method according to claims 1 or 2, c h a r a c t e r i z e d in that the measuring chamber comprises one at least partially transparent wall part and one opposite wall part reflecting incoming radiation, said wall parts being located in the radiation transmission path. 5. A method according to any one of claims 1-4, c h a r a c t e r i z e d in that the adjustment in shape of the measuring cham¬ ber comprises displacement of one of the measuring chamber wall parts located in the radiation trans- mission path. 6. A method according to any one of claims 1-4, c h a r a c t e r i z e d in that the adjustment in shape of the measuring cham- ber comprises displacement of two opposite measur¬ ing chamber wall parts located in the radiation transmission path. 7. A method according to any one of claims 1-6, c h a r a c t e r i z e d in that the transmitted radiation is wide-band radia¬ tion comprising at least one wavelength at which the analyte absorbs. 8. A method according to any one of claims 1-7, c h a r a c t e r i z e d in transmitting radiation at a wavelength additional to the at least one wavelength from the radiation source through the measuring chamber and to the radiation detector and determining the difference between the first and second radiation path lengths on the basis of the radiation detected at each of the wavelengths in each of the measuring steps. 9. A method according to any one of claims 1-8, c h a r a c t e r i z e d in that the analyte is C0 2 . 10. A method according to claim 9, c h a r a c t e r i z e d in using radiation at the wavelengths around 4228 nm, 4268 nm and 4308 nm with a band width of approx. 20 nm. 11. An analyzer with a radiation source, a radiation detector and a measuring chamber device with a measuring chamber, said measuring chamber having at least one at least partially transparent wall part and being in optical communication with the radia- tion source and the radiation detector, c h a r a c t e r i z e d in that the measuring chamber is adjustable in shape, that the analyzer is provided with means which are adapted to adjust the measuring chamber in shape in a controlled manner and which when activated set first and second radiation path lengths, respec¬ tively, across the measuring chamber, and that the radiation source is adapted to transmit radiation at at least one wavelength through the measuring 5 chamber to the radiation detector at the respective first and second radiation path lengths. 12. An analyzer according to claim 11, c h a r a c t e r i z e d in 10 that the radiation path length across the measuring chamber is set by the shape adjustment means inter¬ acting with at least one wall part of the measuring chamber and displacing this wall part. 15 13. A measuring chamber device with a measuring chamber for use in an analyzer according to claims 11 or 12, c h a r a c t e r i z e d in that the measuring chamber is adjustable in shape 2 . 0 in a controlled manner setting first and second radiation path lengths across the measuring cham¬ ber. 14. A measuring chamber device according to claim 13, 5 c h a r a c t e r i z e d in that the optical transmission characteristics of the measuring chamber wall parts adapted to be placed in the radiation transmission path are es¬ sentially independent of the adjustment in shape of 0 the measuring chamber. 15. A measuring chamber device according to claims 13 or 14, c h a r a c t e r i z e d in that the measuring chamber comprises two opposite at least partially transparent wall parts. 16. A measuring chamber device according to claims 13 or 14, c h a r a c t e r i z e d in that the measuring chamber comprises one at least partially transparent wall part and one opposite wall part reflecting incoming radiation.

Inventors: FRISCHAUF PETER AAGE, FRISCHAUF, PETER, AAGE
Applicants: RADIOMETER AS, RADIOMETER A/S
Application year: 1992
Main classification: G01N21
IPC codes: G01N21, G01N35