Device and method for determining sedimentation rate

Abstract

Device and method for determining sedimentation rate A device for determining sedimentation rate comprises at least one member (8) for collecting a blood sample, and a sensor (20) comprising an infrared light source (12) and an optical sensor (14) arranged substantially opposite each other around a substantially transparent portion (16) of the sampling member (8) so that the light emitted by the infrared light source (12) reaches the optical sensor (14) after passing through said substantially transparent portion (16). The optical sensor (14) is arranged to carry out a blank measurement, the device further comprising a converter (10) arranged to receive one or more light transmission measurements from the optical sensor (14), to calculate the ratio between the blank measurement and the one or more light transmission measurements and to return a sedimentation rate. Fig.1

Description

Title of the invention: Device and method for determining sedimentation rate

[0001] The invention relates to the field of hematology, and more particularly to the determination of the sedimentation rate (hereinafter ESR, also called "erythrocyte sedimentation rate" or "ESR" in English).

[0002] The sedimentation rate is part of routine examinations with the complete blood count (hereinafter CBC or NFS for "Completed Blood Count" in English) carried out during a blood test and allows the presence of inflammatory or infectious pathologies to be detected. For example, rheumatism, cancer and other conditions causing changes in the concentration of proteins in the blood. A high ESR indicates an inflammatory state without prejudging its nature. However, it happens that the ESR remains low while there is an inflammatory syndrome. A high ESR therefore generally indicates the presence of a pathology. The combination of this non-specific test with additional examinations allows for a more precise diagnosis.

[0003] The reference method for measuring ESR is the Westergren method. A narrow tube of standardized dimensions is filled with a blood sample taken with an anticoagulant, for example EDTA, and diluted with sodium citrate and placed vertically. The ESR measurement is the height, in millimeters, of the plasma column after one hour of sedimentation. For example, a height of less than 10 mm after the first hour of sedimentation is considered a normal value for an adult male. The limit of normality is not an absolute value but depends on the age and sex of the patient.

[0004] The ESR is the result of three stages: aggregation of red blood cells, sedimentation, and compaction of the rouleaux.

[0005] The phenomenon of aggregation of red blood cells is produced in particular by blood proteins with a force that is all the greater as the concentrations of the latter are high. The formation of aggregates is the stacking of red blood cells into "rolls", then into three-dimensional structures. The sedimentation rate depends on the dimensions of the aggregates and the viscosity of the plasma.

[0006] During the last stages, the aggregates will sediment, that is to say they will gradually fall to the bottom of the tube, then compact, which will have the effect of separating the sample into a clear translucent portion (plasma), at the top, and a much darker portion (red blood cells) at the bottom. The ESR is measured by the height of the translucent portion.

[0007] The most relevant inflammatory parameter is the aggregation phenomenon which is directly dependent on the concentrations of plasma proteins. It is this phenomenon which is measured by the present invention to return an ESR value. It is also a non-specific parameter, but which eliminates interference resulting from the last two stages of the ESR. There is no standardized parameter allowing this speed or dynamics / kinetics of aggregation to be expressed. It is therefore relevant to transpose aggregation measurement quantities into ESR.

[0008] Due to the quantity of blood (1.6 ml) and the time required to perform it (1 hour), the Westergren method is not compatible with automated hematology analyzers for CBC analysis. To circumvent these problems, research has been conducted to use optical extinction measurements (absorption and diffusion) to determine the sedimentation rate, as in US patent 6,632,679.

[0009] Certain patents, as described in EP 2 921 862 have proposed to integrate a modified ESR measurement into a blood testing device which takes a quantity of blood and separates it into two portions which are respectively subject to a count (NFS) and a measurement of sedimentation rate.

[0010] This device therefore links the counting measurement and that of the sedimentation rate measurement, which is disadvantageous because it requires complex equipment to distribute, via a single sample, two portions of blood samples to the counting section on one side and to the sedimentation rate measurement section on the other, especially since the CBC and ESR measurement operations do not present the same needs in terms of sample preparation.

[0011] Some patents, such as the one described in WO 2011 / 101815, have proposed portable devices for implementing a measurement of the sedimentation rate by measuring the transmittance. This device uses single-use capillaries but requires a blood suction system for the measurement. In addition, their method of introducing the capillary makes the device not very ergonomic. In addition, the measurement of transmittance poses problems of accuracy due to the use of capillaries.

[0012] No known device makes it possible to carry out a determination of sedimentation rate in a rapid, repeatable manner and with a simple architecture.

[0013] The invention improves the situation. To this end, it proposes a device for determining sedimentation rate comprising at least one member for collecting a blood sample, and a sensor comprising an infrared light source and an optical sensor arranged substantially opposite one another around a substantially transparent portion of the collection member so that the light emitted by the infrared light source reaches the optical sensor after passing through said substantially transparent portion, the optical sensor being arranged to performing a white measurement, the device further comprising a converter arranged to receive one or more light transmission measurements from the optical sensor, to calculate the ratio between the white measurement and the one or more light transmission measurements and to return a sedimentation velocity.

[0014] This device is particularly advantageous because it allows the sedimentation rate measurement to be determined in a repeatable manner.

[0015] According to various embodiments, the invention may have one or more of the following characteristics:

[0016] - the converter is arranged to determine a transmission measurement instant lowest light transmission measurement time, and a final light transmission measurement time, - the optical sensor is arranged to implement a maximum gain between the lowest light transmission measurement time and the final light transmission measurement time, and to implement a minimum gain the rest of the time, - the converter is arranged to calculate the sedimentation rate from the ratio between, on the one hand, the ratio between the white measurement and the measurement at the final transmission measurement instant, and on the other hand, the ratio between the white measurement and the measurement at the lowest light transmission measurement instant, - the optical sensor is controlled with a low gain before blood passes into the substantially transparent portion, and with a high gain after, - the sampling organ is a needle which can be controlled for the collection of a blood sample to which is connected a tube in which the substantially transparent portion is made, - the infrared light source and the optical sensor are arranged at a distance from the sampling end of the needle of less than 10 cm,

[0017] - the device is arranged to carry out a rinsing of the needle and the tube between two determinations of sedimentation rate measurements, - the sampling member is a capillary, and in which the sensor has a bore arranged to receive said capillary and - the capillary has a lug designed to come into contact with the sensor.

[0018] The invention also relates to a method for determining sedimentation rate comprising the following operations: (a) take a blood sample, (b) passing the blood sample through a substantially transparent portion disposed between an infrared light source and an optical sensor, c) measure one or more light transmissions during operation b) (d) perform a blank measurement in the absence of a blood sample, and e) calculate the ratio between the white measure and the one or more measures of light transmission and derive a sedimentation velocity from it.

[0019] Operation d) can be performed before operation c).

[0020] Other characteristics and advantages of the invention will appear more clearly on reading the following description, taken from examples given for illustrative and non-limiting purposes, taken from the drawings in which:

[0021] - [Fig.l] represents a general schematic view of a device according to the invention, - [Fig.2] represents a detail of the embodiment of an element of [Fig.l], - [Fig.3] represents a measurement diagram using the device of [Fig.l], - [Fig.4] represents a schematic view of a first embodiment of the device of [Fig.l], and - [Fig.5] represents a schematic view of a second embodiment of the device of [Fig.l].

[0022] The drawings and the description below contain, for the most part, elements of a certain character. They may therefore not only serve to better understand the present invention, but also contribute to its definition, where appropriate.

[0023] [Fig. 1] represents a general schematic view of a device 2 for counting blood formula and determining the measurement of sedimentation rate according to the invention. The device 2 comprises a first group 4, a second group 6, a sampling member 8 and a converter 10.

[0024] The first group 4 is arranged to take a blood sample in a tube and to mainly perform a blood count on this sample. This measurement can be carried out in a conventional manner and known elsewhere. Many hematology devices are specialized in carrying out this measurement. Other types of blood tests than CBCs can be carried out within group 4, such as measurements of glycated hemoglobin (HbAlc), C-reactive protein (CRP), etc.

[0025] The second group 6 is arranged to determine a measurement of VS. It is this second group which is the main subject of the invention. Indeed, as described in the introduction, this test, whether carried out according to the conventional method or by measuring the change in light absorbance, is either tedious or coupled with a CBC measurement, which slows down the entire device.

[0026] The implementation of the second group 6 according to the invention makes it possible to extrapolate a measurement of sedimentation rate by changing the light absorbance in a manner decoupled from any CBC measurement or other blood measurements. For this, the second group 6 is arranged to control the sampling member 8 which is here a needle independently of the first group 4, that is to say that the samples taken by the first group 4 are only used for a CBC measurement or other blood measurements, and the samples taken by the second group 6 are only used only for ESR measurement.

[0027] Thus, as can be seen in [Fig. 1], the first group 4 or the second group 6 controls the needle 8 to take a blood sample from a blood tube 11. Then, this sample is brought to the first group 4 to carry out a CBC measurement or other blood measurements, or to the second group 6 to carry out a measurement of change in light absorbance. In the latter case, the measurement is transmitted to the converter 10 which returns an ESR signal and / or a VS measurement value.

[0028] [Fig. 2] represents an exemplary embodiment of the second measuring group 6. According to this example, the second measuring group 6 is produced by means of an optical source 12 and an optical sensor 14 which are assembled facing each other around a tube 16 which serves to transport the blood sample taken by the needle 8 from a blood tube 11 towards the interior of the device 2.

[0029] In the example described here, the light source 12 is of the LED type with an infrared wavelength, preferably in the range 700-980 nm and in particular 800 nm, which is an isosbestic point between oxyhemoglobin and deoxyhemoglobin, which makes the measurement insensitive to the level of oxygen saturation of the blood. In the example described here, the optical sensor 14 is of the photodiode type and can be chosen from PMT, PDA, CMOS sensors, etc. In the example described here, the tube 16 is made of Teflon and is connected to the needle 8. Alternatively, the tube 16 can be made of glass or plastic and must be chosen so as to offer good transparency to the wavelength of the light source 12.

[0030] The light source 12 and optical sensor 14 assembly can be seen as a single sensor 20 of the second group 6. As in the example described here, it can be in two parts which assemble to enclose the needle 8 (for example metallic) and the tube 16. Alternatively, the light source 12 and the optical sensor 14 can be made in one piece. Preferably, the sensor 20 is arranged fairly close to the end of the needle 8, less than 10 cm from it, in order to optimize the shearing of the red blood cells. Preferably, this distance is approximately 5 cm to obtain the best results. In a variant, the sensor 20 can be placed directly at the outlet of the needle 8.

[0031] Whatever the configuration, the second group 6 makes it possible to advantageously use the diameter of the needle 8 which is conventionally of the order of 1 mm. Indeed, during a sample collection by the needle 8, the red blood cells undergo successive deformations which are described below and which are represented in [Fig.3].

[0032] Thus, once the needle 8 is immersed in the blood tube 11, the second group 6 controls aspiration by the needle 8 already primed with diluent in order to collect blood. This is achieved using automation control means, pre-tanks preparation and solenoid valves and syringes known elsewhere and not shown for reasons of simplification. These means cause the displacement of the diluent which occupies the tube 16. At this stage, due to the translucent nature of the tube 16 and the diluent which it contains, the sensor 20 measures a constant optical signal.

[0033] Then, the aliquot of blood is moved to the sensor 20 by suction. The red blood cells undergo shearing, which breaks the aggregation. At this stage, the optical signal remains at a maximum since the blood is not yet facing the sensor 20. In [Fig. 3], this is shown with the reference 30.

[0034] When the blood arrives in the sensor, the optical signal represents the sheared state of the blood. At this stage of blood shearing, the red blood cells have an elongated shape, as visible with reference 31.

[0035] When the suction stops in order to stop the shearing, the optical transmission signal decreases because the red blood cells return to their relaxed biconcave disc shape. In [Fig. 3], this is represented with the reference 32. Then, the optical signal increases according to a pseudo-logarithmic progression. The progressive increase in the optical signal measured by the optical sensor 14 is linked to the progressive aggregation of the free red blood cells. The aggregation is done by the stacking of the red blood cells forming rolls then three-dimensional structures which is represented in [Fig. 3] with the references 34 and 36.

[0036] Beyond about 40s depending on the blood, aggregation is greatly slowed down and sedimentation begins. This start of sedimentation interferes with the measurement of interest which is aggregation and its correlation with the sedimentation rate. After t4 the aliquot of blood is evacuated, for example by moving the needle 8 above a tank. The blood is thus evacuated and the tube 16 is rinsed with diluent, the tube 16 being at the end of this step entirely filled with diluent as at the start of the procedure described above.

[0037] Four moments are represented in [Fig.3]:

[0038] - before time tl, tube 16 is filled with diluent,

[0039] - the instant tl marks the instant at which the blood arrives at the level of the sensor 20 by as inhalation,

[0040] - time t2 marks the time at which the suction ceases,

[0041] - time t3 marks the time from which the red blood cells have resumed their shape relaxed, and the aggregation begins,

[0042] - time t4 marks the end time of the procedure, with the evacuation of the blood which is again replaced by thinner, as before time tl.

[0043] Observation of [Fig. 3] shows that the optical signal is less significant after time t4, when tube 16 is filled with diluent, than when tube 16 is filled with blood, which may seem paradoxical. This is explained by the fact that in the example described here the optical sensor 14 is conditioned differently before the instant t1 and after the instant t4 of [Fig.3].

[0044] Thus, before time t1 and after time t4, it is determined that the measurement corresponds to a "white" measurement. For this entire period, the optical sensor 14 is conditioned by the converter 10 with a minimal measurement gain.

[0045] The instant t3 corresponds to the lowest point of the period t1-t4, from which the optical signal becomes increasing, which marks, as described above, the beginning of the phenomenon that the invention aims to measure. For this reason, and since the variation of the optical signal remains low between the instant t0 and the instant t1, in the example described here, the optical sensor 14 is conditioned with a minimum gain until the instant t1, then with a maximum gain between the instant t1 and t4, then again with a minimum gain after the instant t4 for the next measurement.

[0046] This is all the more advantageous since, in the embodiment described here, the converter 10 is arranged to determine a measurement based on the optical density of the signal measured by the optical sensor 14. As a reminder, the optical density is defined by the formula DO(t) = log(KI0 / / ( / )) where I(t) is the measurement of the optical sensor at time t and K the maximum gain / minimum gain ratio. More precisely, the converter 10 is arranged to return a measurement of sedimentation velocity based on the DO(t3) / DO(t4) ratio. The Applicant has carried out numerous measurements of sedimentation velocity using the Westergren reference method which allows the converter 10 to associate the measurements thus calculated with a VS value.

[0047] The Applicant has discovered that it is particularly advantageous to use optical density, which makes it possible not to depend on possible variations in the transmittance measurement. The Applicant has also discovered that the converter 10 can also operate from the ratio I(t4) / I(t3), without going through the optical density in the Beer-Lambert sense and by using 10 differently in the calculation.

[0048] The converter 10 can be implemented in various ways, for example in the form of appropriate computer code executed on one or more processors. By processors, it is meant any processor suitable for the calculations described below. Such a processor can be implemented in any known way, in the form of a microprocessor for a personal computer, laptop, tablet or smartphone, a dedicated chip of the FPGA or SoC type, a computing resource on a grid or in the cloud, a cluster of graphics processing units (GPUs), a microcontroller, or any other form suitable for providing the computing power necessary for the implementation described below. One or more of these elements can also be implemented in the form of specialized electronic circuits such as an ASIC. A combination of processor and electronic circuits can also be envisaged.In the case of gradient boosting based machine learning unit, processors . dedicated to machine learning may also be considered. Alternatively, the converter 10 may be an analog computer without programming or computer code strictly speaking.

[0049] Still as a variant, the converter 10 could use a machine learning algorithm, involving or not a neural network (deep or not). This involves associating the intensity measurements of the optical sensor 14 with a sedimentation rate value. This variant can be particularly useful for doing without optical density. Still as a variant, the gain of the optical sensor 14 could be the same for all times of the measurement.

[0050] [Fig.4] represents a schematic view of an embodiment of the device of [Fig.l]. As can be seen in this figure, the device 2 is a conventional hematology apparatus comprising a syringe 40 of diameter 1.5mm, and a syringe 42 of diameter 16mm which are both connected to the needle 8. The sensor 20 has been integrated on the needle 8, so that it covers the end of the tube 16 connected to the needle 8.

[0051] The device 2 of [Fig.4] is suitable for carrying out a CBC measurement, an ESR measurement or both.

[0052] For the CBC measurement, the entire circuit is primed with diluent, then the needle 8 hits the blood tube 11 and takes 10 μl with the syringe 40. The needle 8 is then raised and placed above the preparation tank, then the outside of it is rinsed in this tank, with disposal to the waste. Finally, a mixture of the 10 μL sample with 1 mL of diluent (for example) is distributed immediately after collection in the preparation tank with the syringe 42. This first dilution will then be used in the different preparations to carry out the CBC measurement.

[0053] For the ESR measurement, the procedure is as described above with reference to Figures 1 to 3. The entire circuit is primed with diluent drawn from a reservoir 44, then an air bubble of a few pL is created at the end of the needle 8. The needle 8 is lowered into the blood tube 11 and an aliquot of 50 pL to 100 pL is taken by the syringe 42. The needle 8 is raised, and the aliquot transferred to the sensor 20 and the optical measurement of the aggregation is carried out. Finally, the internal and external rinsing of the needle 8 in a tank is carried out, with disposal in the waste. The blank measurement (10) can be carried out before sampling or at the end of rinsing. The optional comparison of the blank measurements before and after allows for exception management, for example a rinsing control.

[0054] The CBC and ESR cycles are carried out independently of each other, and in particular are subject to a separate sample collection by needle 8: the aliquot for the CBC measurement cannot be used for the ESR measurement and vice versa.

[0055] A mixture of the 10 pL sample with 1 mL of diluent (for example) is distributed immediately after collection from the preparation tank with syringe 42. This first dilution will then be used in the various preparations to carry out the CBC measurement.

[0056] This makes it possible to decouple the two measurements without problematic blood sampling when both measurements are requested. This independence makes the ESR measurement much less disruptive to the throughput of the device 2 and allows integration at lower cost, both materially and humanly.

[0057] [Fig.5] represents another embodiment, suitable for the implementation of a portable apparatus for determining the VS.

[0058] In this embodiment, the sampling member 8 is implemented by means of a single-use capillary 54. This makes it possible to take only a drop of blood from a patient's finger and avoids taking blood by venipuncture.

[0059] The device 2 thus comprises the converter 10 and a housing 50 which houses the sensor 20. Thus, the housing 50 contains the optical source 12 and the optical sensor 14 which are received facing each other around a bore 52 of the housing 50.

[0060] As previously, the light source 12 is of the LED type with an infrared wavelength, preferably in the range 700-980 nm and in particular 800 nm, and the optical sensor 14 is of the photodiode type and can be chosen from PMT, PDA, CMOS sensors, etc.

[0061] As can be seen in [Fig.6], when a capillary 54 is introduced into the bore 52, the blood contained in this capillary can rise by capillarity to the housing 50.

[0062] In the example described here, the capillary 54 is made of Teflon and has a diameter of 0.8 mm. Alternatively, the capillary 54 may be made of glass or plastic and must be chosen so as to offer good transparency to the wavelength of the light source 12. Still as a variant, the diameter of the capillary 54 may be between 0.5 mm (a lower value prevents the formation of large aggregate structures and reduces the optical measurement window too much) and 1.5 mm (a higher value makes the capillary force insufficient).

[0063] In the example described here, the capillary has a lug 56 which abuts against the housing 50 in order to control the entry of the tube 14 into the bore 52. The distance from the lug 56 to the end of the capillary 54 is in the example described here fixed at 15 mm. The limits are defined by the following constraints: too close and the sensor 20 interferes with the collection of blood from the finger, and too far and too great a capillary force is required. Alternatively, the tube 54 could have a marking or another means making it possible to control the placement of the tube 54 in the bore 52. Still as a variant, nothing is provided.

[0064] In this embodiment, the shape of the signal is slightly different since the suction is done by capillarity. Also, [Fig.7], equivalent to [Fig.3], represents the evolution of the measurement of the signal at the output of the optical sensor 14.

[0065] As can be seen in this figure, there are no portions before time t1 and after time t4, since the capillaries are single-use. Thus:

[0066] - reference 1 corresponds to the period before time tl of [Fig.3]. The measurement is carried out through the empty capillary 54, and will constitute the 10 of the calculation in low gain. The transmission on empty capillary 54 is 30 times greater than blood. Under these conditions, it is preferred to keep the high gain / low gain modes.

[0067] - reference 2 corresponds to times t2 to t3 of [Fig.3]. The blood arrives at sensor, and the transmission instantly drops to 0. It is this edge that is detected and can be used to control the switch from low gain to high gain.

[0068] - reference 3 corresponds to the instants after instant t3 of [Fig.3]. The blood circulates in the capillary. It is in a sheared state. The slight slope is due to the slowing down of the blood and therefore the shear.

[0069] - reference 4 corresponds to the end of the sample. The blood having passed the sensor, the user removes the system. The separation between the capillary and the drop of blood “abruptly” stops the capillary rise. This results in a peak, then a drop (pointed out by reference 4), and

[0070] - reference 5 corresponds to the aggregation phase.

[0071] The converter 10 can be connected to any type of interface, for example a laptop, notebook, etc. The interface can also be of the smartphone type with a dedicated application. In this case, the sensor 20 incorporates the optical components and electronic resources allowing interfacing with a standard means of communication, USB for example. The interface can also be a proprietary system. This solution allows a human-machine interface perfectly adapted to the need, as well as the reduction to the strict minimum of the components embedded in the sensor (LED and photodiode). Preferably, a touch screen is used, which in particular allows for a virtual keyboard for entering identifiers and other information relating to the analysis carried out.

Claims

Claims

1. Device for determining sedimentation rate, comprising at least one blood sample collection member (8), and a sensor (20) comprising an infrared light source (12) and an optical sensor (14) arranged substantially opposite each other around a substantially transparent portion (16) of the collection member (8) so that the light emitted by the infrared light source (12) reaches the optical sensor (14) after passing through said substantially transparent portion (16), the optical sensor (14) being arranged to carry out a blank measurement, the device further comprising a converter (10) arranged to receive one or more light transmission measurements from the optical sensor (14), to calculate the ratio between the blank measurement and the one or more light transmission measurements and to return a sedimentation rate.

2. Device according to claim 1, wherein the converter (10) is arranged to determine a lowest light transmission measurement instant (t3), and a final light transmission measurement instant (t4).

3. Device according to claim 2, in which the optical sensor (14) is arranged to implement a maximum gain between the instant of measurement of lowest light transmission (t3) and the instant of measurement of final light transmission (t4), and to implement a minimum gain the rest of the time.

4. Device according to claim 2 or 3, in which the converter (10) is arranged to calculate the sedimentation rate from the ratio between on the one hand the ratio between the white measurement and the measurement at the final transmission measurement instant (t4), and on the other hand the ratio between the white measurement and the measurement at the lowest light transmission measurement instant (t3).

5. Device according to claim 2, in which the optical sensor (14) is controlled with a minimum gain before blood passes into the substantially transparent portion, and with a maximum gain after, and this until the final light transmission measurement time (t4).

6. Device according to one of the preceding claims, in which the sampling member is a needle (8) which can be controlled for the sampling of a blood sample to which a tube is connected (16) in which the substantially transparent portion (16) is made.

7. Device according to claim 6, wherein the infrared light source (12) and the optical sensor (14) are arranged at a distance from the sampling end of the needle (8) of less than 10 cm.

8. Device according to one of claims 6 and 7, arranged to carry out a rinsing of the needle (8) and the tube (16) between two determinations of sedimentation rate measurements.

9. Device according to one of claims 1 to 5, in which the sampling member (8) is a capillary (54), and in which the sensor (20) has a bore (52) arranged to receive said capillary (54).

10. Device according to claim 9, in which the capillary (54) has a lug (56) arranged to come into abutment against the sensor (20).

11. A method for determining sedimentation rate comprising the following steps: a) taking a blood sample, b) passing the blood sample through a substantially transparent portion disposed between an infrared light source and an optical sensor, c) measuring one or more light transmissions during step b) d) performing a blank measurement in the absence of a blood sample, and e) calculating the ratio of the blank measurement to the one or more light transmission measurements and deriving a sedimentation rate therefrom.

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