PATENT DOCUMENT

Abstract:
A disposable cartridge for characterizing particles suspended in a liquid, especially a self-contained disposable cartridge for single-use analysis, such as for single-use analysis of a small quantity of whole blood. The self-contained disposable cartridge facilitates a straightforward testing procedure, which can be performed by most people without any particular education. Furthermore, the apparatus used to perform the test on the cartridge is simple, maintenance free, and portable.

Full Description:
CROSS REFERENCE TO RELATED APPLICATIONS 
     This application claims priority under 35 U.S.C. 119 to Danish application PA 2003 00159 filed on Feb. 5, 2003, and under 35 U.S.C. 119(e)(1) to U.S. Provisional application Ser. No. 60/387,407 filed on Jun. 11, 2002, which are hereby incorporated by reference. 
    
    
     BACKGROUND OF THE INVENTION 
     1. Field of the Invention 
     The present invention relates to a disposable cartridge for characterizing particles suspended in a liquid, especially a self-contained disposable cartridge for single-use analysis, such as for single-use analysis of a small quantity of whole blood. The self-contained disposable cartridge facilitates a straightforward testing procedure, which can be performed by most people without any particular education. Furthermore, the apparatus used to perform the test on the cartridge, could be made simple, light and maintenance free, thus giving full portability and a large range of operation for the user. The invention provides steps for pre-analytic handling of samples such as hemolysing of red blood cells and inactivation of coagulation. 
     2.Description of the Background Art 
     Present instruments for particle characterization such as counting and sizing are fairly expensive, immobile and require operation by trained personnel. The consequence hereof has been that many instruments are placed in dedicated laboratories that are operated by specialized personnel. Furthermore, the samples to be analysed must be transported to this laboratory and the results are reported back to the requiree. 
     In WO 01/11338, which is hereby incorporated by reference, an apparatus is disclosed for characterizing particles suspended in a liquid, comprising a disposable cartridge and a docking station for removably receiving the cartridge. The cartridge comprises a housing with a first collection chamber bounded by a wall containing an orifice for the passage of the particles and having an inlet/outlet for connection to a source of positive or negative gas pressure, and components of a particle characterization device for characterizing particles passing through the orifice that are connectable from outside the housing. The docking station comprises a port for connection with a source of positive or negative gas pressure and forming a gas connection with the inlet/outlet when the cartridge is received in the docking station, and means for operative connection with the components of a particle characterization device when the cartridge is received in the docking station. 
     In WO 02/089670, which is hereby incorporated by reference, a device for sampling a small and precise volume of liquid is disclosed, comprising a movable member with a cavity for entrapment and displacement of an accurate part of a liquid sample. 
     It is a disadvantage of these prior art devices that several devices are used to perform an analysis, e.g. of a whole blood sample. The sample taking is performed with a separate device, and the sample has to be transferred to another device for sample preparation before it is finally transferred to a sensor for analysis. 
     In WO 99/01742 a disposable sampling device is disclosed for an apparatus for counting particles contained in a liquid. The sampling device is connectable in a defined position to the apparatus. The device has means for introducing a sample therein, means for metering a defined volume of the sample, means containing a defined volume of a diluting liquid, a diluting chamber, means for simultaneously directing the defined volume of sample and the defined volume of diluting liquid to the diluting chamber for obtaining therein a diluted sample, means for directing at least a portion of the diluted sample past particle counting means and signal transmitting means connecting the particle counting means and terminal means located at an outer boundary of the housing in a position corresponding to a location of terminal means of the apparatus when the housing is connected thereto in the defined position. 
     During blood analysis with the device described in WO 99/01742, the blood sample is pumped back and forth several times for dilution, mixing and analysis, and the flow system is closed so that the pressure in the system is increased and decreased above and below, respectively, atmospheric pressure during movement of the sample. Further, sample taking requires pumping with a membrane or another flow actuator causing entrance of blood into the flow system of the device. Thus, the above disclosed flow system is rather complicated. 
     The particle counting is, as described in WO 99/01742, performed in an open-ended tube so that the volume of diluted sample passing the particle counting sensor is very small. 
     The blood analysis, as described in WO 99/01742 does not take into account that particles of different kind and concentration might need pre-analytic separation, decomposition, staining or labeling in order to be accurately recorded by the sensing principle in account. 
     The blood test sequence as described in WO 99/01742 does not take into account that users without prior education herein should be able to learn how to perform this test themselves, i.e. no pre-analytical dilution steps should be required. 
     SUMMARY OF THE INVENTION 
     Thus, it is an object of the present invention to provide a cartridge for characterizing particles suspended in a liquid that enables sample taking, sample preparation, and particle characterization so that analysis may be performed within one device without a need for sample handling and sample transfer to another unit. 
     It is a further object of the present invention to provide a cartridge that is adapted for single-use to be discarded after analysis of one liquid sample. 
     It is another object of the present invention to provide a cartridge that has a simple flow system. 
     It is yet another object of the present invention to provide a flow system in the cartridge communicating with the surroundings so that the pressure in the flow system remains substantially constant at atmospheric pressure. 
     According to the present invention, the above-mentioned and other objects are fulfilled by a cartridge for characterizing particles suspended in a liquid, comprising a housing with a first mixing chamber and a first collection chamber separated by a wall containing an orifice for passage of the particles between the first mixing chamber and the first collection chamber. Particle characterization means are provided for characterizing particles passing through the orifice. 
     Sample taking may be performed through a bore in the outer surface of the housing for entrance of a liquid sample. The housing further comprises a sampling member that is movably positioned in the housing. The sampling member has a first cavity for receiving and holding a small and precise volume of liquid. In a first position of the sampling member, the first cavity is in communication with the bore for entrance of the liquid sample into the first cavity, and, in a second position of the sampling member, the first cavity is in communication with an inlet to the first mixing chamber. 
     Thus, the sampling member operates to receive and hold a precise volume of liquid sample and to transfer the sample to the inlet of the first mixing chamber. 
     Preferably, liquid to be sampled enters the cavities by capillary attraction causing a liquid flow. Utilization of capillary forces simplify the flow system, since no pumps, membranes, syringes or other flow generating means are, in contrast to WO 99/01742, needed to take the sample. 
     Thus, the bore may form a first capillary tunnel for entrance of a liquid sample by capillary attraction. The capillary tunnel is dimensioned so that, upon contact between the bore and liquid to be sampled, a sample of the liquid is drawn into the bore by capillary attraction. 
     Further, the first cavity may form a second capillary tunnel adapted for drawing the liquid sample into the first cavity by capillary attraction. Preferably, the first and second capillary tunnel has the same diameter, and it is also preferred that, in the first position, the first and second capillary tunnel extend along substantially the same longitudinal center axis. 
     Preferably, the sampling member is rotatable about an axis of rotation that is substantially perpendicular to a longitudinal axis of the first cavity. 
     Additionally or alternatively, the sampling member may be displaced in a direction substantially perpendicular to a longitudinal axis of the first cavity. 
     The surface of the first and second inner capillary tunnel walls may be hydrophilic whereby the capillary attraction of the liquid sample is facilitated. For example, the inner tunnel walls may be made of e.g. glass or polymers, such as polystyrene. 
     Alternatively, the capillary tunnel walls may be made of another type of material and covalently or non-covalently coated with a hydrophilic material, such as a polymer or a reagent. 
     The capillary tunnel may also include one or more reagents adhered or chemically bonded to the inner tunnel wall. These reagents serve the purposes of further facilitating the capillary attraction of the sample and optionally also causing a chemical reaction in the liquid sample, e.g. introducing anticoagulant activity in a blood sample. Such reagents may comprise heparin, salts of EDTA, etc. 
     Preferably, the sampling member is made of a polymer. 
     In accordance with a further aspect of the invention, an apparatus is provided for characterizing particles suspended in a liquid, comprising a cartridge as disclosed herein, and a docking station for removably receiving the cartridge, the docking station comprising connectors for operational connection with the particle characterization means when the cartridge is received in the docking station. 
     The cartridge may further comprise a cartridge port communicating with the first collection chamber for causing a liquid flow through the orifice, and the docking station may further comprise a corresponding port for forming a gas connection with the cartridge port when the cartridge is received in the docking station for application of a pressure causing a liquid flow through the orifice. 
     The particle characterization means may include a first electrode in the first mixing chamber and a second electrode in the first collection chamber, each electrode being electrically connected to a respective terminal member accessible at the outer surface of the cartridge for operational connection to the respective connector of the docking station when the cartridge is received in the docking station. Generally, it is preferred that all necessary electrical and fluid connections to the cartridge can be established by fitting the cartridge into the docking station, preferably by a simple push fit. 
     The first and second electrodes may facilitate particle characterization utilizing the well-known Coulter impedance principle, e.g. for counting and sizing of blood cells. This method has become a globally accepted method and is being used in the majority of haematology-analysers. Several thousand particles per second may be characterized with high precision and accuracy utilizing this principle. 
     With the electrical impedance technique it is possible to resolve the particle volume from the measurement. By maintaining a constant current across the orifice, the recorded voltage pulse from particles displacing the electrolyte in the orifice will have a height proportional to the volume of the particle. This is because particles can be considered non-conducting compared to the electrolyte, the electrical field (DC or RF) in the centre of the orifice is homogeneous, which is normally the case when the diameter D is smaller than the length l of the orifice (I/D&gt;1), the particle d is to be considered small compared to the diameter of the orifice (d&lt;0.2*D), only one particle passes through at a time and the particles are passed through the orifice along the length of the orifice. 
     Normally such apparatus is operated so that the flow through the orifice is into the first collection chamber. 
     Preferably, the length of the orifice is from 1 to 1000 μm, for example about 50 μm. Desirably the length of the orifice is chosen such that only one particle will be present in the orifice at the time when detecting particles of from 0.1 to 100 μm diameter. However, considerations to the homogeneity of the electrical field in the orifice may require a length of the orifice larger or equal to the diameter. The counts, of which some may be simultaneous counting of two particles, can be corrected mathematically by implementing a statistical estimation. The aspect ratio of the orifice, (length or depth divided by diameter) is preferably from 0.5:1 to 5:1, more preferably from 1:1 to 3:1. 
     Preferably, the largest cross-sectional dimension of the orifice is from 5 to 200 μm, for example 10 to 50 μm. 
     As explained above, the present invention provides in preferred aspects a sensor based on a membrane fabricated in e.g. a polymer sheet by laser ablation. The membrane has an orifice placed relatively in the centre of the membrane, which can be used for aspiration of particles suspended in a liquid, as the sensor is submerged into the liquid. This way of transporting particles into a measuring region is known for electrical characterization of particles by the Coulter principle (V. Kachel, “Electrical Resistance Pulse Sizing: Coulter Sizing”, Flow Cytometry and Sorting, 2. ed., pp 80, 1990 Wiley-Liss, Inc.). 
     The cartridge may further comprise a breather inlet/outlet communicating with the surroundings for preservation of substantially ambient atmospheric pressure in the cartridge flow system for facilitation of liquid flow through the orifice. 
     Preferably, the cartridge is designed to be disposable after a single use. It is desirable that after use there is no need to clean the apparatus before it can be used in a new assay procedure with a new cartridge. Accordingly, escape of liquid from the cartridge at its entry into the docking station should be avoided. To this end the positioning of the orifice with respect to the breather inlet/outlet, the second chamber inlet/outlet and the particle characterization device components is preferably such that a volume of liquid sufficient for the desired particle characterization can be drawn or pumped through the orifice without the liquid passing out of the housing. Generally, it should be possible to pass a volume of liquid, which is at least 0.1 ml to 10 ml, e.g. 0.5 ml, through the orifice whilst particle characterization measurements are being made with no liquid leaving the cartridge. 
     The cartridge may comprise volume-metering means for determining the beginning and end of a period during which a predetermined volume of liquid has passed through the orifice. 
     Preferably, the volume metering means comprises a volume-metering chamber with an input communicating with the first collection chamber and an output, and wherein presence of liquid is detected at the input and at the output, respectively. 
     For example, presence of liquid may be detected optically due to changed optical properties of a channel configuration from being filled with air till when it is being filled with liquid. This could be constructed as reflectance or transmittance detection from the surface, where incident light is reflected from an empty channel and transmitted through a filled channel, thus giving a clear shift in the detected reflected or transmitted light. 
     It is preferred that the input and output of the metering chamber is formed by narrow channels for accommodation of only a small liquid volume compared to the volume of the metering chamber so that the actual positioning of the volume metering means, e.g. optical reflectance detection, in the channels do not substantially influence the accuracy of the volume metering means determination. 
     The first mixing chamber or the first collection chamber may constitute the volume metering chamber; however, it is preferred to provide an independent volume metering chamber facilitating positioning of the volume metering means, e.g. the optical reflectance detection. 
     The volume metering means may be positioned for sensing when liquid in the metering chamber is at or above respective levels in the volume-metering chamber. 
     The volume metering means may be used for sensing when the level of the liquid is such that the respective metering means are or are not filled with the liquid and may therefore serve for determining the beginning and end of a period during which a fixed volume of liquid has passed through the orifice. For example, particle characterization may begin when the level of the liquid just rises over the level of a first metering means and may end when the level of the liquid just rises over a second metering means, the volume of liquid passing through the orifice during this period being defined by the separation of the respective metering means. 
     Where the end point of the passage of a defined volume of liquid is the effective emptying of one chamber to below the level of the orifice, it is preferred that each of the collection and first mixing chambers (or at least that chamber from which liquid passes) has a transverse cross sectional area at the level of the orifice which is substantially less than the transverse cross sectional area of the chamber over a substantial part of the height of the chamber above the orifice. 
     According to a further aspect of the present invention a method is provided of operating a particle characterization apparatus comprising a cartridge as disclosed herein, the cartridge being demountable from the apparatus, the method comprising sampling liquid containing particles with the cartridge through the bore with the sampling member in its first position, positioning the cartridge in the apparatus, moving the sampling member to its second position, pumping liquid in the storage chamber through the first cavity and into the first mixing chamber together with the liquid sample, making particle characterizing measurements, disconnecting the cartridge from the apparatus, and discarding the cartridge. 
     Generally, in all embodiments it is preferred that all components, which are wet by the sample in use, are disposable and all non-disposable components can be re-used without cleaning. 
     It is an important advantage of the present invention that means for liquid sample preparation and analysis are integrated into a disposable cartridge. For example, the analytical steps comprise sampling of a precise amount of blood, dilution of the amount of blood and finally mixing the blood with diluent into a homogeneous solution. The analysis may include spectrophotometric analysis of the liquid. 
     Thus, according to the present invention, means are provided for unambiguously making a blood analysis, such as counting the blood cells in a small amount of blood coming from a droplet of capillary blood. Means are provided for taking an exact amount of blood sample, reagents present in the diluent may be added for e.g. dilution and/or chemical preparation of the sample, and the mixed sample and diluent flows through a sensor for analysis of individual blood cells and determination of the volume of the analysed quantum of liquid. 
     As a supplement a spectrophotometric measurement can be performed in order to quantify the content of e.g. haemoglobin. 
     The cartridge may comprise the following parts:
     1. A liquid storage chamber   2. A blood-sampling device   3. A first mixing chamber   4. A flow through sensor arrangement   5. A first collection chamber   6. A volume metering arrangement comprised of a chamber and two connected flow channels   7. A hydraulic connection for moving the liquid through the cartridge   

     The concept of the disposable unit can be further combined with the following additional parts:
     A. Optical structures for optical liquid level measurement   B. Electrodes for liquid level measurement   C. Anti-coagulation treatment of surfaces   D. Reagents in the diluent for modification of e.g. blood cells   E. Mixing flee or baffle for assisted mixing   F. Multiple volume metering arrangements for altering volumes   G. A coating tape covering the sample inlet before use   H. A waste chamber for waste/overflow   I. A valve preventing liquid to exit through exhaust tube   J. An integrated piston or membrane to replace an external source of pressure   K. A window for spectrophotometric measurements   

     The liquid storage chamber (part 1) holds the required amount of diluent used for the blood analysis. When the blood has been sampled into the cartridge, the diluent is flushed through the capillary to wash out the sampled blood and dilute it as required by the test. Dilutions of 100 to 100.000 times are considered to be normal ratings and dilutions of 500 to 10.000 times are preferred. The liquid storage chamber should preferably be constructed to facilitate total draining of the chamber. This would be accomplished by having a slanting of the bottom of the chamber. 
     The sampling unit (part 2) may comprise a capillary extending through a movable rod placed in a tight-fitting supporting body. The movable rod is used for entrapment of a precise amount of blood sample. When blood has filled the capillary by capillary forces, the rod is turned and/or displaced from its initial position in the supporting body, thus isolating the part of the capillary that extends through the rod. 
     After moving the rod in the supporting body into its second position the capillary forms a liquid path between the liquid storage chamber and the first mixing chamber (part 3). By applying a low pressure to the first mixing chamber the diluent and blood sample is forced into the first mixing chamber, where mixing will be performed by convection or subsequently by blowing bubbles into the mixing chamber. 
     The flow through sensor arrangement (part 4) is comprised of a small orifice in a membrane that establishes a liquid path from the first mixing chamber to the first collection chamber. On each side of the membrane (in the first mixing chamber and in the first collection chamber) an electrode is placed contacting the liquid. 
     The first collection chamber (part 5) forms a liquid priming function of the backside of the sensor system. 
     The volume metering system (part 6) is necessary for determination of the cell concentration. It comprises volume-metering chamber of a known volume with two relatively thin channels connecting the inlet at the bottom and the outlet at the top. Sensing of the liquid at the inlet and outlet can be applied by optical or electrical means. 
     The outlet of the volume metering system is connected through a channel (part 7) to a source of pressure for moving the liquid through the cartridge. 
     The additional parts to the concept are further described here: 
     Addition A: Optical detection by change of optical properties of a channel such as changed reflectance or transmittance due to replacement of air with liquid in the channel. The surface over the inlet and outlet of the volume-metering cell should be structured to optimize the coupling of the light into the channel. The presence of liquid in a transparent polymer channel will result in a transmission of the signals as opposed to a reflection when no liquid is present, which can be registered by optical sensors. 
     Addition B: Two electrodes for liquid level measurement are connected through the body of the cartridge into the inlet and outlet of the volume-metering cell respectively. The electrodes will be short-circuited through the saline liquid to the electrode placed in the first collection chamber, which can be registered through an external electrical arrangement. 
     Addition C: The anti-coagulation treatment of surfaces in the sampling structure can be achieved by having selected compounds adhered or chemically bonded to these surfaces. Examples of such compounds are heparin and salts of EDTA. 
     Addition D: Reagent in the diluent for modification of e.g. blood cells. This reagent can consist of one or several compounds capable of hemolysing the erythrocytes. In addition other compounds may be added in order to: stabilize leukocytes and/or thrombocytes, adjust the pH-value and osmotic pressure, minimize bacterial growth, modify the haemoglobin present and minimize batch to batch variations. The following examples have been included to provide information on relevant subjects related to the performance of a self-contained test cartridge. 
     Examples of compounds capable of selectively hemolysing the red blood cells are: mixtures of quaternary ammonium salts as described in e.g. U.S. Pat. Nos. 4,485,175; 4,346,018; 4,745,071; 4,528,274; and 5,834,315. 
     Examples of compounds capable of, during the hemolysis of the red blood cells, stabilizing the leukocytes are N-(1-acetamido)iminodiacetic acid, procaine hydrochloride as described in e.g. U.S. Pat. No. 4,485,175 and 1,3-dimethylurea as described in e.g. U.S. Pat. No. 4,745,071. In addition N-(1-acetamido)iminodiacetc acid is proposed to further assist the quaternary ammonium salts in minimizing debris stemming from hemolysed red blood cells as described in e.g. U.S. Pat. No. 4,962,038 and adjust the pH-value (see below). 
     Examples of compounds added in order to adjust the pH-value and not least importantly the osmotic pressure of the diluent are: N-(1-acetamido)iminodiacetic acid, sodium chloride, sodium sulphate as described in e.g. U.S. Pat. No. 4,485,175 and U.S. Pat. No. 4,962,038. 
     Examples of compounds capable of minimizing bacterial growth are: 1,3-dimethylolurea and chlorhexidine diacetate as described in e.g. U.S. Pat. No. 4,962,038. 
     Examples of compounds added to convert the hemoglobin species to an end-product suitable for spectrophotometric analysis are: potassium cyanide as described in e.g. U.S. Pat. Nos. 4,485,175; 4,745,071; 4,528,274 and tetrazole or triazole as described in WO 99/49319. 
     Examples of particles or compounds which may be added in order to introduce a tool for minimizing variation between different batches of the disposable device are: latex beads of known size and glass beads of known size. 
     Addition E: If assisted mixing is required the first mixing chamber might optionally include a mixing flee or a baffle. A magnetic flee may be used to force the convection through an externally moving magnetic field. A baffle may be used to mechanically stir the liquid when moved by an externally connecting mechanical device. This could be required if mixing with bubbles, such as bubbles blown into the sample through the sensor, is not adequate or possible. 
     Addition F: Multiple volume metering arrangements can be successively included if the test must deal with different concentrations of the different particles. 
     Addition G: A lid or coating tape may be used to cover the sample inlet before use. This ensures a clean sampling area at the origination of the test. 
     Addition H: A waste chamber may be applied at the outlet of the volume-metering cell for waste or overflow of liquid. 
     Addition I: At any connection ports, e.g. the connection port to the pressure source, a small valve can be integrated to prevent liquid to leak out of the cartridge. 
     Addition J: A piston or membrane can be integrated into the cartridge to include a source of pressure for moving the liquid. The piston or membrane could be moved by a mechanical force provided by the instrument. 
     Addition K: An optical window can be integrated into the cartridge in order to perform optical measurements such as spectrophotometric detection of the haemoglobin content in a blood sample. 
     The methods described can be combined to give the best solution for the final application. The disposable sensor is particularly usable where portable, cheap, simple or flexible equipment is needed, such as in small laboratories, in measurements in the field or as a “point of care” (“near-patient”) diagnostic tool. 
     When using the Coulter principle the diluent for use in the apparatus according to the invention may contain inorganic salts rendering the liquid a high electrical conductivity. When sample is applied to the electrolyte, the electrolyte to sample volumes should preferably be higher than 10. Sample preparation should preferably result in between 1.000 to 10.000.000 particles per ml and more preferably between 10.000 and 100.000 particles per ml. A mixing of the sample after adding electrolyte is recommended. Particle diameters should preferably be within 1 to 60 percent of the orifice diameter and more preferably between 5 to 25 percent of the orifice diameter. Volume flow should preferably be from 10 μl to 10 ml per minute and more preferably between 100 μl and 1 ml per minute. For the measurement a constant electrical current of approximately 1 to 5 mA should preferably be applied. The source of electrical current should preferably have a signal to noise ratio (S/N) better than 1.000. The response from the electrodes can be filtered electronically by a band-pass filter. 
     According to yet another aspect of the invention a cartridge is provided comprising a housing with a first mixing chamber and a first collection chamber separated by a wall containing a first orifice for the passage of the particles between the first mixing chamber and the first collection chamber, first particle characterization means for characterizing particles passing through the first orifice, a bore in the outer surface of the housing for entrance of the liquid sample, communicating with a first sampling member positioned in the housing for sampling the liquid sample and having a first cavity for receiving and holding the liquid sample, the member being movably positioned in relation to the housing in such a way that, in a first position, the first cavity is in communication with the bore for entrance of the liquid sample into the first cavity, and, in a second position, the first cavity is in communication with the first mixing chamber for discharge of the liquid sample into the first mixing chamber. 
     The cartridge may further comprise a second mixing chamber and a second collection chamber separated by a second wall containing a second orifice for the passage of the particles between the second mixing chamber and the second collection chamber, second particle characterization means for characterizing particles passing through the second orifice. 
     In one embodiment of the invention, the first cavity is in communication with the first mixing chamber, when the first sampling member is in its first position, for entrance of liquid from the first mixing chamber into the first cavity, and, in a third position of the first sampling member, the first cavity is in communication with the second mixing chamber for discharge of the liquid in the first cavity into the second mixing chamber. 
     In another embodiment of the invention, the cartridge further comprises a second sampling member positioned in the housing for sampling a small and precise volume of liquid from the first mixing chamber and having a second cavity for receiving and holding the sampled liquid, the member being movably positioned in relation to the housing in such a way that, in a first position, the second cavity is in communication with the first mixing chamber for entrance of liquid from the first mixing chamber into the first cavity, and, in a second position, the second cavity is in communication with the second mixing chamber for discharge of the sampled liquid in the second cavity into the second mixing chamber. 
     The cartridge may further comprise a reagent chamber positioned adjacent to the first mixing chamber for holding a reagent to be entered into the first mixing chamber. 
     Preferably, the cartridge further comprises a breakable seal separating the reagent chamber from the first mixing chamber. 
     With this embodiment, different chemical treatment of different parts of the liquid sample may be performed. 
     Also with this embodiment, further dilution of the liquid sample may be performed. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS The invention will be further described and illustrated with reference to the accompanying drawings in which: 
         FIG. 1  shows a cross sectional side view through the components of a disposable unit  85 , referred to as the cartridge, 
         FIG. 2  shows the flow-through sensor concept  FIG. 3  comprises an apparatus based on the disposable cartridge, a docking station  66  and a reader  74 , 
         FIG. 4  shows the cartridge with a build in piston, 
         FIG. 5  schematically illustrates the sampling procedure, 
         FIG. 6  is a plot of results obtained in Example 1, 
         FIG. 7  is a plot of results obtained in Example 2, 
         FIG. 8  is a plot of results obtained in Example 3, 
         FIG. 9  is a plot of results obtained in Example 4, 
         FIG. 10  is a plot of results obtained in Example 5, 
         FIG. 11  is a schematic illustration of the cartridge and hydraulic connections in example 6, 
         FIG. 12  is a plot of the process described in example 7, 
         FIG. 13  is a plot of the process described in example 8, 
         FIG. 14  shows schematically a second embodiment of the cartridge, 
         FIG. 15  shows schematically a third embodiment of the cartridge, and 
         FIG. 16  shows in perspective an apparatus according to the invention. 
     
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
     
       FIG. 1 
     
     A disposable cartridge with a housing  85  for blood analysis comprises a liquid storage chamber  1  containing a liquid diluent  11 , a first sampling member  2  positioned in the housing  85  for sampling a blood sample  8  and having a cavity  10  for receiving and holding the blood sample  8 , the member  2  being movably positioned in relation to the housing  85  in such a way that, in a first position, the cavity  10  is in communication with a bore  90  for entrance of the blood sample  8  into the cavity  10  by capillary forces, and, in a second position, the cavity  10  is in communication with the liquid storage chamber  1  and a mixing chamber  3  for discharge of the blood sample  8  diluted by the liquid diluent  11  into the mixing chamber  3 . The mixing chamber  3  is separated by a wall containing an orifice  59  from and a collection chamber  5  for the passage of the blood sample  8  between the mixing chamber  3  and the collection chamber  5 . The wall containing the orifice  59  constitutes a part of a flow-through sensor  4 . 
     A volume metering arrangement is connected to the collection chamber comprising a volume metering chamber  6  having the size of the volume to be measured during the measurement with two connecting channels  12 ,  13  of relatively diminutive internal volumes for registering liquid entry and exit by optical or electrical means, from the volume metering chamber a channel  7  leads out to a connection port  67  where a pressure can be applied. 
     
       FIG. 2 
     
     The flow-through sensor  4  has a dividing wall  91  with a relatively narrow orifice  59  for the passage of particles suspended in liquid. The orifice serves as a sensing zone for detection and measurement of the individual cells. The orifice in the sensor may be formed as a count orifice for counting and sizing particles by an impedance method known as Coulter counting. Particles can be aspirated through the orifice by pressure driven flow in either direction. When a saline or other electrolytic liquid solution is added to the chambers, the two chambers will be electrically isolated from each other except for the route for current flow provided by the passage through the orifice. 
     
       FIG. 3 
     
     The chambers on each side of the flow through sensor may have electrodes  34 ,  35  extending from an external terminal  61 ,  62  through the base wall  63  of the disposable unit and into a configuration facing the inside of its respective chamber. The cartridge is placed in a docking station  66  in a portable apparatus in order to carry out the test. The docking station  66  has a cup shaped housing having a base  70  and a circumambient sidewall  71 . In the base  70  there are respective spring loaded electrical connectors  64 ,  65  for contacting the terminals  61 ,  62  of the cartridge automatically when the cartridge is received as a push fit into the docking station. There is also a conduit  68  passing through the base wall  70  aligned with the conduit  67  of the cartridge. Conduit  67  at its opening into the upper face of the wall  70  has a seal  69 , such as e.g. an O-ring for forming a gas tight connection with the lower face of the base wall  63  of the cartridge. A vacuum pump  72  is connected by a line  73  to the lower end of the conduit  68 . In a modification of the apparatus, the vacuum pump  72  can be reversed so as to apply positive gas pressure to the conduit  68 . Schematically indicated at  74  are the further conventional components of a Coulter counter including all the electronic circuitry and display equipment needed for the operation of the apparatus. A general perspective view of the cartridge and reader is shown in  FIG. 16 . 
     
       FIG. 4 
     
     As an alternative to the gas pump a piston  9  could be build into the cartridge for directly appliance of a negative or positive pressure. 
     
       FIG. 5 
     
       FIG. 5  schematically illustrates the blood sampling operation. The illustrated part of the cartridge  2  includes the liquid storage chamber  83  for storing a diluent for diluting the sample and the first mixing chamber  77  for mixing the sample  84  and the diluent. This figure schematically illustrates a device for sampling a small and accurate volume of liquid in accordance with the present invention. The device  10  comprises a first member  86  with a first opening  87  for entrance of a liquid sample into a bore  75  in the first member  86  and with a second opening  76  for outputting the liquid sample from the bore  75 . The bore  75  forms a capillary tunnel. The first opening  87  of the first member  86  may be brought into contact with a liquid  8  (shown in  FIG. 1 ),  84  to be sampled so that the liquid  84  may flow through the first opening  87  into the bore  75  and out of the second opening  76  by capillary attraction. The device  12  further comprises a sampling member  78  with a first cavity  82  for receiving and holding the liquid sample  84  and having a third opening  88  communicating with the first cavity  82 . The first cavity forms a capillary tunnel with essentially the same diameter as the bore  75 . The sampling member  78  is a circular cylinder that is movably positioned in relation to the first member  86 . During sampling of the liquid, the sampling member  78  is positioned in the illustrated first position in relation to the first member  86  wherein the second opening  76  is in communication with the third opening  88  so that sampled liquid may flow through the second  76  and third opening  88  into the first cavity  82  by capillary attraction. The third opening  88  may be disconnected from the second opening  76  in a second position of the sampling member  78  in relation to the first member  86  so that the liquid sample  84  contained in the first cavity  82  is disconnected from the bore  75 . 
     The sampling member  78  is inserted into a third cavity of the first member  86  for receiving and accommodating a part of the sampling member  78 . The sampling member  78  may be displaced between the first and second position along a longitudinal axis of the sampling member  78  that is also substantially perpendicular to a longitudinal axis of the first cavity  82 . The sampling member  78  may also be rotatable about a longitudinal axis that is substantially perpendicular to a longitudinal axis of the first cavity  82 . In the first position, the first  75  and second  82  capillary tunnels extend along substantially the same longitudinal center axis. 
     In the illustrated embodiment the first member  86  is symmetrical and has a fourth cavity  80  with openings  81 ,  79  opposite the bore  75 , and the sampling member  78  has an opening  89  opposite the opening  88  so that, in the first position, a capillary tunnel extends through the first  86  and the second  78  member and communicates with the environment through openings  87 ,  79 . Thus, air may escape from the capillary tunnel through opening  79 . Further, in the first position, a part of the liquid entering the first cavity  82  will leave the cavity  82  through opening  89  thereby ensuring that the cavity  82  has been completely filled with liquid during liquid sampling eliminating the risk of sampling with a reduced sample volume leading to low accuracy sampling. 
       FIG. 5   a  illustrates the device  2  ready for receiving the liquid. In  FIG. 5   b , a sample has entered into the capillary tunnel  82 , and in  FIG. 5   c  the sampling member  78  has been rotated into the second position for isolation of an accurate volume of the sample  84 , and finally  FIG. 5   d  illustrates that the sample  84  has been washed out of the capillary tunnel  82  and into the first mixing chamber  77  by the diluent. 
     Example 
     The capillary tunnel forming the first cavity  82  may have a length of 8 mm and a diameter of 0.9 mm for containing a liquid sample of 5.089 μL. 
     Example 
     The capillary tunnel forming the first cavity  82  may have a length of 5 mm and a diameter of 0.5 mm for containing a liquid sample of 0.982 μL. 
     Example 
     The capillary tunnel forming the first cavity  82  may have a length of 3 mm and a diameter of 0.3 mm for containing a liquid sample of 0.212 μL. 
     
       FIG. 6 
     
     Example 1 
     Sizing of Polymer Beads 
     A mixture of 5 μm and 10 μm particles suspended in electrolyte was aspirated through the orifice of the apparatus shown in  FIG. 3 . The numbers of particles detected and the size of each detected particle were recorded. A bimodal distribution of detected particle size is clearly seen in  FIG. 6 . 
     
       FIG. 7 
     
     Example 2 
     Red Blood Cell Counting 
     Measurement of blood cells has been performed and the result is shown in  FIG. 7 . Red blood cells are normally around 5 to 7 μm in diameter and are the most frequent in whole blood, as can be seen on the  FIG. 7 . The distribution is a Gaussian curve, as it should be expected. Blood counts can be used in clinical diagnostics. It is fairly simple to count erythrocytes, leukocytes and thrombocytes by impedance measurements, which are considered the basic parameters for haematology (see “Fundamentals of Clinical Haematology”, Stevens, W.B. Saunders Company, ISBN 0-7216-4177-6). 
     
       FIG. 8 
     
     Example 3 
     White Cell Counting using a Diluent Containing a Reagent-Composition Selected so as to Preserve all Blood Cells 
     Material 
     Cartridge and apparatus containing the functions as described in the present invention, 
     Isoton, Beckman Coulter (prod. no. 24655) containing: sodium chloride 7.9 g/L, potassium chloride 0.4 g/L, disodiumhydrogenphosphate 1.9 g/l, sodiumdihydrogenphosphate 0.2 g/L, disodium-EDTA 0.4 g/L and sodium fluoride 0.3 g/L. 
     Vacutainer, K3E, Becton &amp; Dickinson, prod. No. 367652. 
     Bayer, ADVIA-120 equipment. 
     Performance 
     The full sequence of the procedure was as follows:
         Collection of a venous blood sample in a vacutainer tube.   Leaving the sample, for the sedimentation process to proceed, for three hours.   Extraction the plasma phase with the major part of the buffy-coat section included   Performing analysis using the Bayer Advia  120  equipment for obtaining a comparative value for the content of leukocytes.   Adding 5.00 ml isoton solution as diluent to the chamber of the test rig   Adding 10.0 μl of sample to the chamber   Mixing liquids in the chamber   Starting test sequence on the computer (starts the pump and readies the sampling)   When the liquid reaches the first level electrode sampling is started   When the liquid reaches the second level electrode the sampling is stopped   Sampled values are saved in a file   The file is opened with a “pulse-viewer” for data analyzing and calculation of the result using a method of calculation involving subtraction of, with the leukocytes overlapping red blood cells.       

     Results
     Bayer Advia-120: 11.96×10^9 leukocytes/L   Test-rig: 11.92×10^9 leukocytes/L   Difference in accuracy: (11.96−11.92)/11.96=0.33%   

     
       FIG. 9 
     
     Example 4 
     White Cell Isolation using a Diluent Containing a Reagent Composition Selected so as to Primarily Hemolyse the Red Blood Cells 
     Material 
     Cartridge and apparatus containing the functions as described in the present invention, 
     Diluent containing: procaine hydrochloride 0.10 g/L, 1,3-dimethylolurea 0.90 g/L, N-(1-acetamido)iminodiacetic acid 1.28 g/L, dodecyltrimethyl ammonium chloride 7.51 g/L and sodium chloride 0.03 g/L. 
     Vacutainer, K3EDTA, Becton &amp; Dickinson, prod. No. 367652. 
     Performance 
     The full sequence of the procedure was as follows:
         Collection of a venous blood sample in a vacutainer tube.   Leaving the sample, for the sedimentation process to proceed, for three hours.   Extraction the plasma phase with the major part of the buffy-coat section included   Adding 2.000 ml diluent as described above to the chamber of the test rig   Adding 4.0 μl of sample to the chamber   Mixing liquids in the chamber   Starting test sequence on the computer (starts the pump and readies the sampling)   When the liquid reaches the first level electrode sampling is started   When the liquid reaches the second level electrode the sampling is stopped   Sampled values are saved in a file   The file is opened with a “pulse-viewer” for data analyzing and generation of the result.
 
Results
       

     As can be seen in the histogram in  FIG. 6  the particle population corresponding to the leukocytes is easily identified in the absence of the red blood cells. 
     
       FIG. 10 
     
     Example 5 
     Counting Somatic Cells 
     Milk quality is essential for farmers, diary producers and consumers. Farmer has to deliver milk of a certain quality, which is controlled by the so-called Somatic Cell Count (SCC). In milk quality tests somatic cells in the milk are counted to determine infections (clinical mastitis). A limit of 400.000 cells pr. ml. has to be met by the farmers for dairy resale. Change of diet, stress or mastitis lead to higher SCC levels, thus lowering the quality of the milk and consequently lowering the price per unit volume. A cheap cell counter will help farmers and diary producers monitor SCC-level. 
     
       FIG. 11 
     
     Example 6 
     A Blood Diagnostic System 
     This is an example of a 3 part differential white blood cell count (monocytes, lymphocytes, granulocytes), thrombocytes count and haemoglobin measurement and the corresponding instrumentation and cartridge realized through the present invention. 
     A three-part differentiation of white blood cells, thrombocyte counter with measurement of haemoglobin can be achieved with the specified components. 
     A reagent for selectively lysing red blood cells is added to the diluent in the storage chamber  1 . When the whole blood  8  is added to the opening  58  of the first capillary section  15 , the blood will be dragged in to the capillary and through the middle section  10  and last section  14  of the capillary. The last section of the capillary is connected to a fill-chamber  43  for visually verification of the filling. The fill-chamber  43  is connected through a conduct  44  to open air. 
     The blood filled middle section of the capillary is part of a knob  2  that can be moved to a second position, connecting the ends of the capillary to two other conducts, a conduct  45  connected to the storage chamber  1  and a second conduct  40  connected to the first mixing chamber  3  respectively. A third conduct  39  is leading from the first mixing chamber to a port opening  42  in the cartridge. The port opening is connected through a counter port opening  37  in the apparatus, through a tubing  46  to a three-position valve  51  and directed through the two positions of the valve to open air through a second tubing  55  or through a third tubing  50  to the suction port of a membrane pump  47 . 
     When the blood and diluent with reagent has been sucked into the first mixing chamber, the blood can be mixed by blowing bubbles through the orifice of the sensor  4 . The air pressure is applied through the collection chamber  5 , via a fourth conduct  12 A, a small volume chamber  6 A, a fifth conduct  12 B, a large volume chamber  6 B and a sixth conduct  7  directed to an opening port  41  in the cartridge. A counter port  36  in the apparatus is connected through a fourth tubing  48  to a second three position valve  52 , which has positions to direct to both vacuum through a fifth tubing  56  to the suction port of the membrane pump, or to the exhaust of the membrane pump, through a third two position valve  53  and a sixth tubing  49 , the third valve having two positions for the connection and for directing the pump exhaust to open air through a seventh tubing  54  respectively. 
     After mixing the diluted and lysed blood (red blood cells is removed) it is ready to be measured. The first mixing chamber is connected through the first valve to open air and the collection chamber is connected through the second valve to the suction port of the pump. The exhaust of the membrane pump is connected through the third valve to open air. As the blood and diluent flows from the first mixing chamber into the collection chamber, an electrical connection between to counter electrodes  34  and  35  placed in each chamber is established through the liquid. Cells are counted and differentiated by size by the Coulter principle. Through sizing of the cells, the cells can be distinguished and categorised into different groups containing cells of a certain type. Thus white blood cells (leucocytes) can be differentiated into granulocytes, lymphocytes and monocytes. Furthermore, thrombocytes (platelets) can be differentiated from leucocytes as well. In order to determine the concentration, the volume of the diluted blood, which has been counted, must be known. Since thrombocytes are approximately ten times as frequent as leucocytes, it may be necessary to measure two different volumes. The thrombocytes are counted according to a small volume chamber  6 A positioned between the collection chamber and the larger volume. By registering the liquid entry and exit at the inlet and outlet of the small volume chamber respectively, the counting period will be given. Registration of the liquid level is preferably done by an optical reflectance measurement at the inlet  33  and at the outlet  32 . The outlet of the small volume chamber is also the inlet of the large volume chamber  6 B. This chamber is used in connection with counting of leucocytes. At the outlet of the large volume chamber, a third optical reflectance measurement  31  is performed to register the exit of the liquid from this chamber. 
     After counting both leucocytes and thrombocytes the haemoglobin content can be measured by optical spectroscopy preferably through the middle section of the large volume chamber  30 . 
     Process of the test (example 6): 
     The process of making a test by means of the present invention can be characterized as:
         1) Draw blood by using a lancet device   2) Pick up blood droplet by touching the blood to the cartridge inlet   3) Mount cartridge in the instrument (instrument starts and runs the test)   4) Read the result from the display   5) Remove and discard cartridge       

     
       FIG. 12 
     
     Example 7 
     Photolithography 
     An orifice may suitably be formed in a photo-reactive polymer by photolithography and subsequent development. Thus a free standing sheet of polymer of the kind used conventionally as a photo resist material may be exposed to light to render a spot to soluble to define an orifice (or to render the non-spot forming areas in-soluble) followed by development with solvent to remove material to form the orifice. Normally, a large number of count wafers each containing a respective orifice will be made simultaneously in one sheet. Suitable photo resist polymers are described in e.g. M. Madou “Fundamentals of Micro fabrication, CRC Press LLC, 1997, ISBN 0-8493-9451-1. They include AZ-5214E, SU8, polyamides and others. 
     Alternatively, the photo resist polymer may be used as a protecting layer over a substrate such as silicon in which the orifice is formed by etching regions exposed by development of the photo resist. If the etched substrate is electrically conducting it may be insulated prior to use by the formation of a suitable insulating layer there over. The photo resist polymer may be used as such a layer. 
     Count wafers made lithographically may be used in all forms of apparatus and method according to this invention.  FIG. 12  shows one process of fabricating the count wafer: (a) appliance of a thin sheet of photo resist. (b) Development of the mask. (c) Etching of the orifice by Deep Reactive Ion Etching (DRIE, M. Madou “Fundamentals of Micro fabrication, CRC Press LLC, 1997, ISBN 0-8493-9451-1). 
     
       FIG. 13 
     
     Example 8 
     Orifice Fabricated by Laser Micro Machining 
     Orifices for Coulter counting can be fabricated by laser micro machining of polymers, which could lead to a simple and convenient way of fabricating and assembling orifices for the cartridge. A series of small holes of 50 μm has been fabricated with an UV-laser. The holes are made in less than 1 ms in a 50 μm polymer sheet. The uniformity of the holes is very high and the smoothness of the orifice entrance is unique.  FIG. 13  shows the process of laser machining of the orifice. The laser cuts through the polymer foil in a circle, thus defining the size of the orifice. 
     
       FIG. 14 
     
       FIG. 14  shows schematically a preferred embodiment of the cartridge according to the invention. The illustrated cartridge has a first member  104  for sampling blood. The member  104  is movably positioned in relation to the housing between three positions, a first position for blood sampling, a second position to connect the first storage chamber  103  with the first mixing chamber  112 , and a third position to connect the second storage chamber  105  with the second mixing chamber  110 . The blood is passed through the bore  122  into the first cavity of the member  104  by capillary forces or by applying a vacuum at the end of the sampling channel  111 . A liquid blocking valve  116  is arranged after the first sampling member to hinder passage of blood through the channel. After the blood sampling, the sampling member is turned to the second position and the sample is flushed into the first mixing chamber  112  by the liquid in the first storage chamber  103 . In the first mixing chamber  112  the sample is diluted 1:200 with the liquid in the first storage chamber  103  and a fraction is blown back into the first cavity of the sampling member  104 , which is turned to the third position so that the diluted sample is flushed into the second mixing chamber  110  by the liquid in the second storage chamber  105 . In the second mixing chamber  110  the sample is further diluted 1:200 to a total dilution of 1:40.000 with the liquid in the second storage chamber  105 . A hemolysing reagent is injected into the first mixing chamber  112  by a piston  115 , which breaks a seal  118  between a reagent chamber  119  and the first mixing chamber  112 . After hemolysing the blood the 1:200 diluted sample is ready for counting non-hemolysed white blood cells and for measuring hemoglobin by photometry. The white cells are counted by passing them through a first orifice  113  and measuring the response by impedance cell counting over a first electrode pair  117 ,  120 . A fixed volume is counted by a first volume metering arrangement  107  connected to the first collection chamber  114 . A first overflow volume  106  is arranged after the first volume metering arrangement  107 . The white blood cells can be differentiated by volume after adding the lysing reagent to the blood. The white cells can be grouped by volume into: Granulocytes, Monocytes and Lymphocytes. The three groups together yield the total white cell count. 
     In the second mixing chamber  110 , red cells and platelets are counted. The red cells and platelets are counted by passing them through a second orifice  109  and measuring the response by impedance cell counting over a second electrode pair  121 ,  125 . A fixed volume is counted by a second volume metering arrangement  101  connected to the second collection chamber  108 . A second overflow volume  102  is placed after the second volume metering arrangement  101 . 
     The embodiment may further comprise an additional optical detector for photometric determination of the hemoglobin content. Referred to simply as “total hemoglobin”, this test involves lysing the erythrocytes, thus producing an evenly distributed solution of hemoglobin in the sample. The hemoglobin is chemically converted to the more stable and easily measured methemoglobintriazole-complex, which is a colored compound that can be measured calorimetrically, its concentration being calculated from its amount of light absorption using Beer&#39;s Law. The method requires measurement of hemoglobin at approx. 540 nm where the absorption is high with a turbidity correction measurement at 880 nm where the absorption is low. 
     
       FIG. 15 
     
       FIG. 15  shows schematically another preferred embodiment of the cartridge according to the invention. The illustrated cartridge has a first member  104  for sampling blood. The member  104  is movably positioned in relation to the housing  100  between two positions, a first position for blood sampling, and a second position to connect the first storage chamber  103  with the first mixing chamber  112 . A blood sample is passed through the bore  122  into the first cavity of the member  104  by capillary forces or by applying a vacuum at the end of the sampling channel  111 . A liquid blocking valve  116  is arranged after the first sampling member to hinder passage of blood through the channel. After the blood sampling, the sampling member is turned to the second position and the sample is flushed into the first mixing chamber  112  by the liquid in the first storage chamber  103 . In the first mixing chamber  112  the sample is diluted 1:200 with the liquid in the first storage chamber  103 . 
     The cartridge further comprises a second sampling member  123  positioned in the housing  100  for sampling a small and precise volume of liquid from the first mixing chamber  112  and having a second cavity  123  for receiving and holding the sampled liquid, the member  123  being movably positioned in relation to the housing  100  in such a way that, in a first position, the second cavity  123  is in communication with the first mixing chamber  112  for entrance of a diluted sample from the first mixing chamber  112  into the second cavity  123 , and, in a second position, the second cavity  123  is in communication with the second mixing chamber  110  so that the diluted sample is flushed into the second mixing chamber  110  by the liquid in the second storage chamber  105 . In the second mixing chamber  110  the sample is further diluted 1:200 to a total dilution of 1:40.000 with the liquid in the second storage chamber  105 . A hemolysing reagent is injected into the first mixing chamber  112  by a piston, which breaks a seal between a reagent chamber and the first mixing chamber  112 . The piston, seal and reagent chamber are not shown in  FIG. 15 . After hemolysing the blood the 1:200 diluted sample is ready for counting non-hemolysed white blood cells and for measuring hemoglobin by photometry. The white cells are counted by passing them through a first orifice  113  and measuring the response by impedance cell counting over a first electrode pair  117 ,  120 . A fixed volume is counted by a first volume metering arrangement  107  connected to the first collection chamber  114 . A first overflow volume  106  is arranged after the first volume metering arrangement  107 . The white blood cells can be differentiated by volume after adding the lysing reagent to the blood. The white cells can be grouped by volume into: Granulocytes, Monocytes and Lymphocytes. The three groups together yield the total white cell count. 
     In the second mixing chamber  110 , red cells and platelets are counted. The red cells and platelets are counted by passing them through a second orifice  109  and measuring the response by impedance cell counting over a second electrode pair  121 ,  125 . A fixed volume is counted by a second volume metering arrangement  101  connected to the second collection chamber  108 . A second overflow volume  102  is placed after the second volume metering arrangement  101 . 
     The embodiment may further comprise an additional optical detector for photometric determination of the hemoglobin content. Referred to simply as “total hemoglobin”, this test involves lysing the erythrocytes, thus producing an evenly distributed solution of hemoglobin in the sample. The hemoglobin is chemically converted to the more stable and easily measured methemoglobintriazole-complex, which is a colored compound that can be measured calorimetrically, its concentration being calculated from its amount of light absorption using Beer&#39;s Law. The method requires measurement of hemoglobin at approx. 540 nm where the absorption is high with a turbidity correction measurement at 880 nm where the absorption is low.