Patent Publication Number: US-2022214270-A1

Title: Device and process for screening of a biological sample

Description:
FIELD OF THE INVENTION 
     The present invention relates to a device for the screening a biological sample contained in a container which is housed by a transport device and which has at least one label attached to one of its surfaces. 
     PRIOR ART 
     Nowadays, in clinical laboratories the need to ensure a high level of precision in the analysis of biological samples is increasing. 
     A biological sample is usually transported along an automated transport line comprising an automatic conveyor belt, in order to be sent to the appropriate analyzers. 
     Biological sample containers can be of different types. For the sake of simplicity the following discussion refers to a test tube, supported by a suitable transport device able to be transported along the belt. 
     The biological sample contained in the test tube, before being sent to the analyzers, must be centrifuged so that the separation between the liquid part (plasma or serum) and the corpuscular part takes place, such parts being eventually separated by the separation gel if originally present in the test tube. 
     Once the sample has arrived at an analyzer, generally the determination of the value of a specific analyte is carried out by means of spectrophotometric techniques, taking care to prepare in advance an aliquot of the content of a parent test tube, which is separated into one or more children cuvettes. 
     The analysis is then carried out on a cuvette, placed between a radiation source and a photodiode. The result of the analysis is obtained by reading the value of a signal received by the photodiode after the signal itself, emitted by the radiation source, has passed through the cuvette. 
     Problems arise because often a biological sample is already corrupt from the beginning by the presence of alterations of some specific parameters, which can affect the result of the analysis carried out by the analyzer. 
     In particular, among such alterations there may be “serum indices” such that, in the case the biological sample under examination is serum or plasma, it has an abnormal color. For example, three cases are known, corresponding with three distinct types of alteration:
         Hemolysis (hereinafter “H”), whereby the serum has a bright red color due to the breakdown of red blood cells;   Icterus (“I”), whereby the serum has an intense yellow color due to an excess of bilirubin in the blood, especially visible in individuals subject to hepatic diseases;   Lipemia (“L”), whereby the serum has a milky white color due to the presence of lipids in the blood.       

     There are several known possibilities for detecting in advance the presence of such alterations. 
     A first solution is that in which the expert laboratory staff performs a visual analysis of the sample, looking for the respective characteristic colors of the serum in the three cases described above. In case of evident presence of one of the three factors, the altered biological sample is discarded, since its analysis would lead to unavoidably corrupt results. Of course, visual analysis involves a significant waste of time for laboratory staff, which delays the performance of other functions. 
     A second solution is to perform the screening of the alteration indices on the analyzer. Even this solution however, besides often requiring a significant use of reagents, involves a waste of time since, if the screening of the aforementioned indices gives a positive result, the results of other analyses performed by the analyzer would also be considered unreliable, that is the analyzer would have worked in vain. Furthermore, a screening performed by the analyzer involves a waste of time even if it has a positive result, due to the need to prepare an aliquot of the sample and to lift it from the transport device that houses it to take it to a station for the spectrophotometric analysis. 
     In known devices for the screening of a given parameter (or analyte) in a biological sample, it is usual to illuminate the sample with a known radiation and to detect the intensity of the radiation transmitted downstream of the sample and detected by a detection system, for example a photodiode. 
     Each type of detectable parameter shows, by virtue of its nature, a different response depending on the wavelength of the radiation that hits it. Each parameter therefore shows a characteristic curve, which indicates absorption peaks at specific wavelengths, experimentally determined. To detect the presence of a certain parameter it is then particularly suitable to irradiate the biological sample, contained in a test tube, with a radiation at the wavelength for which the characteristic curve of such parameter shows an absorption peak: in this way, in fact, a significant decay of the signal detected by the photodiode downstream of the test tube is a symptom of an absorption of the radiation by the sample, and therefore of the presence within the sample itself of the parameter under examination. 
     In order to proceed with an analysis for H, I or L in blood serum, absorption curves are observed, obtained experimentally for each one of the three indices, shown in the graph represented in  FIG. 10  of the drawings annexed to this description. 
     As already mentioned, it is useful to carry out the analysis of each of the indices based on a wavelength where the absorption shows a peak: in this way, the serum sample hit by a radiation with a wavelength corresponding to the peak shows an output signal characterized by a considerable attenuation, indicating the presence of the indicator of interest (H, I or L as appropriate). By way of example, the characteristic absorption spectrum for H is shown in  FIG. 11 . 
     However, if the analysis is performed by limiting it to the maximum absorption wavelength only, therefore having as unique result an intensity value of the transmitted light, the result itself is influenced by other parameters, such as the physical characteristics of the test tube. The result can indeed be affected, for example, by the size of the inspection window, that is of the typically rectangular area on the surface of the test tube which is actually hit by the radiation. A greater size of such area is linked with a greater amount of transmitted radiation. Similarly, other physical factors that can affect are the size (and eventually the number, if more than one is present) of the labels placed on the test tube, as well as the orientation with which they are applied. Furthermore, the material the test tube is made of may also influence the passage of radiation or not. 
     For these reasons, it is good to carry out the analysis by detecting not only the signal intensity at the wavelength of the absorption peak, but also at a reference wavelength. A ratio is then made between the two intensities, taking care that the values for the two different wavelengths have been obtained with the same aforementioned physical conditions of the test tube, so that they do not influence. 
     The signal is typically detected by a camera that acquires images of the sample and that works in the visible spectrum (from 440 nm to 700 nm). Therefore it is necessary to stay in this wavelength range. 
     A device that exploits the ratio between the transmitted intensities of a reference radiation and an absorption radiation, according to the mechanism described above, to screen a biological sample and, in particular, to detect the presence of serum indices, is for example described in document U.S. Pat. No. 7,688,448 B2. In this known solution, anyway, the transmission of the radiation through the biological sample can be influenced by any lack of homogeneity of the container surface or labels attached to it, with the risk of affecting the precision and accuracy of the detection. EP 3 018 482 A1 describes a detection device configured to detect color and quantity of a plurality of components which constitute a biological sample. The present invention starts from the desire to overcome some drawbacks of the prior art. 
     Object of the Invention 
     The object of the present invention is to provide a device for the screening of a biological sample of the type indicated at the beginning of the present description able to perform an accurate and precise analysis even in presence of labels or inhomogeneities on the surface of the container of the sample analyzed. 
     A further object of the present invention is to provide a device of the type above indicated which allows to automate the screening operations of a biological sample and to speed up the whole analysis procedure. 
     A further object of the present invention is to provide a device of the type above indicated which is simple and cheap to use. 
     SUMMARY OF THE INVENTION 
     In view of achieving one or more of the aforementioned objects, the invention relates to a device for the screening a biological sample having the characteristics indicated in claim  1 . 
     In an embodiment, the filter holder device comprises at least two filters for selecting respectively an absorption radiation with a wavelength of 450 nm and a reference radiation with a wavelength of 660 nm, in order to detect the presence of lipemia in the biological sample. 
     In another embodiment, the filter holder device comprises at least two filters for selecting respectively an absorption radiation with a wavelength of 575 nm and a reference radiation with a wavelength of 660 nm, in order to detect the presence of hemolysis in the biological sample. 
     In another embodiment, the filter holder device comprises at least three filters for selecting respectively a first absorption radiation with a wavelength of 575 nm, a second absorption radiation with a wavelength of 520 nm and a reference radiation with a wavelength of 660 nm, in order to detect the presence of icterus in the biological sample. 
     In the preferred embodiment, the filter holder device comprises at least four filters for selecting three absorption radiations with wavelengths of respectively 450 nm, 520 nm and 575 nm, and a reference radiation with a wavelength of 660 nm, in order to detect the presence of hemolysis, icterus and lipemia in the biological sample by performing a single analysis. 
     Preferably, the filter holder device comprises at least one further black filter, in order to perform a quality control on the radiation emitted by the radiation source. 
     In the preferred embodiment, the filter holder device is a filter holder wheel. 
     According to a further characteristic of the preferred embodiment, the backlight panel and the radiation source are light-emitting diodes (LEDs). 
     Preferably, the automated transport line is able to transport the transport device housing the container downstream of the analysis station up to an analyzer. 
     In the preferred embodiment, the automated transport line comprises a station located downstream of the analysis station and upstream of the analyzer, able to remove containers marked as unacceptable following the analysis carried out in the analysis station. 
     The invention also relates to a process for the screening of a biological sample having the characteristics indicated in claim  11 . 
     Preferably, the process is carried out using a filter holder device provided with filters with absorption and reference wavelengths already indicated above, for the purpose of detecting the presence of hemolysis, icterus or lipemia within a biological sample, by making separate analyses or by making a single analysis. 
     Preferably the process further comprises the transport, by means of the automated transport line, of the transport device housing the container up to an analyzer located downstream of the analysis station. 
     In the preferred embodiment, the process further comprises the removal of the samples marked as unacceptable following the analysis carried out in the analysis station. This removal is performed in a station located downstream of the analysis station and upstream of the analyzer. 
    
    
     
       DETAILED DESCRIPTION OF EMBODIMENTS OF THE INVENTION 
       Further features and advantages of the invention will become apparent from the following description with reference to the annexed drawings, given purely by way of non-limiting example, in which: 
         FIG. 1  is a perspective view of the device for the screening of a biological sample according to the present invention, 
         FIG. 2  is a raised side view of the analysis station of the device according to the present invention, 
         FIG. 3  is a side view of the lighting system of the device according to the present invention, 
         FIG. 4  is a perspective view of the lighting system of the device according to the present invention, 
         FIG. 5  is a perspective view of the rotation system of the device according to the present invention, 
         FIG. 6  is a perspective view of the rotation system of the device according to the present invention rotated by 180° with respect to the view of  FIG. 5 , 
         FIG. 7  is a front view of the container of the biological sample with the sample volume and the inspection window in evidence, 
         FIG. 8  is a front view of the container of the biological sample with the label in evidence, 
         FIG. 9  is a diagram of the radiation path in the device according the present invention, 
         FIG. 10  is a representation of the absorption curves obtained experimentally for H, I and L in blood serum, 
         FIG. 11  is a representation of the characteristic absorption spectrum of H,
           FIG. 12  is a representation of a graph in which the parameters relating to H obtained using the device according to the present invention are related with the parameters detected by a reference analyzer, which expresses the results in mg/dl,     FIG. 13  is a representation of a graph that highlights the correlation between the results relating to an analysis for H on blood serum samples performed using the device according to the present invention and the same analysis performed using a reference laboratory analyzer,     FIG. 14  is a representation of a graph in which the parameters relating to I obtained using the device according to the present invention are related with the parameters detected by a reference analyzer, which expresses the results in mg/dl, and     FIG. 15  is a representation of a graph in which the parameters relating to L obtained using the device according to the present invention are related with the parameters detected by a reference analyzer, which expresses the results in mg/dl.       

     
    
    
     In  FIG. 1 , the number  1  generally indicates a device for the screening a biological sample according to the present invention. In the embodiment shown, the device  1  comprises an analysis station  3  and a lighting system  4 , which cooperate with each other to obtain the detection of a light signal. The device  1 , furthermore, comprises an automated transport line  2  comprising an automatic conveyor  5  for advancing a biological sample contained in a container  6  through the analysis station  3 . 
     In the preferred embodiment, the automated transport line  2  is able to transport the container  6  downstream of the analysis station, up to an analyzer (not shown). 
     With reference in particular to  FIG. 2 , in the embodiment shown the analysis station  3  comprises a camera  30  having a lens  31 , a front illuminator  32  and a backlight panel  33 , preferably LED. It must be understood that the camera  30  can be any other known optical detector, for example a video camera. The lens  31  is placed between the camera  30  and the front illuminator  32 , laterally and orthogonally with respect to the path of the container  6  of biological sample along the automated transport line  2 . The backlight panel  33  is placed facing the front illuminator  32 . As shown in  FIG. 1 , the device  1  also comprises an electronic controller E, able to process signals emitted by the camera  30 . 
     In the preferred embodiment the container  6  of biological sample is a test tube. However, this feature is not to be intended in a limiting sense, since the container  6  can be any known container of a biological sample, for example a cuvette or a centrifuge tube. 
     As visible in  FIG. 1 , in the preferred embodiment the lighting system  4  is located below the side covers of the automatic conveyor  5 . Anyway, this feature is not to be intended in a limiting sense, since the lighting system  4  can be arranged in any position with respect to the automatic conveyor  5  such as not to interfere with the transport of the container  6  along the automated transport line  2 . 
     As visible in  FIGS. 3 and 4 , in the embodiment shown the lighting system  4  comprises a radiation source  50 , preferably LED, a filter holder device  51 , comprising at least two filters for selecting at least two radiations with different wavelengths emitted by the radiation source  50 , and an optical coupler  52 . Preferably, the aforementioned elements are aligned vertically on each other in this order ( FIG. 3 ), in an area hidden from view, with the radiation source  50  at the base. 
     The lighting system  4  and the analysis station  3  are connected by means of an optical fiber  53 , having a first end connected with the lighting system  4  and a second end connected with the analysis station  3 . In the preferred embodiment, the outlet of the optical fiber  53  in the analysis station  3  is located above the group consisting of the camera  30  and the lens  31  ( FIG. 2 ). The optical fiber  53  is able to convey the radiation emitted by the radiation source  50  towards the container  6  located in the analysis station  3 . 
     As shown in  FIG. 4 , in the preferred embodiment, the filter holder device is a filter holder wheel  51  comprising 4 different filters  510 ,  511 ,  512  and  513 , able to select respectively the following wavelengths: 450 nm, 660 nm, 575 nm and 520 nm. It is, furthermore, present a black filter  514 . However, the scope of the present invention also covers embodiments in which the filter wheel comprises a number of filters different from that shown, and in which the filters are able to select different wavelengths from those listed above. Furthermore, the order of the filters to select the above mentioned wavelengths can be different from that shown in the figure. 
     As can be seen in particular in  FIGS. 5 to 8 , the container  6  of biological sample is housed by a transport device  20 . In the embodiment shown, the transport device  20  consists of a series of coaxial cylinders arranged one above the other, whose diameters become smaller and smaller from the bottom to the top. However, this feature is not to be intended in a limiting sense, since the transport device  20  can be any other known transport device for a container  6  of biological sample. 
     As shown in  FIGS. 5 and 6 , in the preferred embodiment the analysis station  3  comprises a rotation system  7 . The rotation system  7  comprises a first roller  70  and a second roller  72 , each located at one of the two opposite sides of the automatic conveyor  5 . When it is necessary to rotate the container  6  housed by the transport device  20 , a first cylinder  71  operates the first roller  70 , which comes out of its seat and protrudes into the space defined by the two opposite sides of the automatic conveyor  5 . In this way, the transport device  20  is pushed by the first roller  70  against the second roller  72 , thus remaining blocked. As can be seen in  FIG. 6 , the rotation system  7  further comprises a motor  73  and a belt  74 , supported by two pulleys  75   a  and  75   b.  The second pulley  75   b  is pushed towards the transport device  20  thanks to the action of a second cylinder  76 . In this way, the belt  74 , kept in rotation by the motor  73 , elastically stretches and presses against the transport device  20 , causing its rotation. 
     As can be seen in  FIG. 7 , in the preferred embodiment the container  6  contains a volume  60  of sample, inside which an inspection window  61  is identified, which corresponds to the area which is irradiated by the radiation emitted by the radiation source  50 . It is to be understood that the sample volume  60  and the inspection window  61  can be different from those shown, for example the container  6  may contain more or less sample volume  60 , and the inspection window  61  can be located in a different point of the sample volume  60  and have a different shape from that shown. 
     As can be seen in  FIG. 8 , a label  600  is attached to the surface of the container  6 . It is to be understood that also embodiments in which the shape and dimensions of the label  600  are different from those represented fall within the scope of the present invention. Furthermore, it is also possible that more than one label  600  is attached to the surface of the container  6 . 
     The invention also relates to a process for the screening of a biological sample contained in a container  6  which is housed by a transport device  20  and which has at least one label  600  attached to a surface thereof, comprising the steps of:
         providing an automated transport line  2  comprising an automatic conveyor  5  able to move forward the transport device  20  housing the container  6  through an analysis station  3 ,   irradiating the container  6  in the analysis station  3  with a radiation emitted by a radiation source  50  and collecting through an optical detector the radiation after it has irradiated the container  6 ,   providing an electronic controller E to process signals emitted by the optical detector to perform the screening of the biological sample contained in the container  6 ,   filtering the radiation emitted by the radiation source  50  selecting a filter between at least two filters carried by a filter holder device located downstream of the radiation source  50 ,   collecting the radiation reflected by a volume  60  of the sample in the container  6  and by the label  600  attached to the container  6  by means of the optical detector  30 , in the form of a camera or video camera, when the label  600  is on the side of the container  6  opposite to that from which the radiation emitted by the optical fiber  53  originates,   preliminarily to the analysis of the biological sample contained in the container  6  performing an optical detection of the container  6 , making use of a backlight panel  33  and a front illuminator  32  placed one in front of the other and able to illuminate the container  6 , and in order to allow the camera or video camera  30  to acquire, and possibly store, at least one image of the container  6 , and to send to the electronic controller E an information on the basis of the acquired image,   rotating the container  6  around a vertical axis, on the basis of the information received from the camera or video camera  30  to position the container  6  so that:   a) the label  600  attached to the surface of the container  6  is arranged on the opposite side with respect to that from which the radiation directed towards the container  6  originates,   b) the emitted radiation irradiates the volume  60  of the sample at a predetermined inspection window  61 .       

     It is to be understood that the aforementioned process can be carried out using any of the embodiments of the device  1  described above. 
     In the preferred embodiment, the process comprises the further step of detecting, by means of a first and a second sensor included in the camera or video camera  30 , the intensity values of the components of reference radiation and absorption radiation which have not been absorbed by the biological sample, and of sending them to the electronic controller E. Preferably, the electronic controller E processes a ratio between the intensity value of absorption radiation not absorbed by the biological sample and the intensity value of reference radiation not absorbed by the biological sample, in any order. 
     In the preferred embodiment, the process comprises the further step of transporting, by means of the automated transport line  2 , the container  6  housed by the transport device  20  downstream of the analysis station  3  up to an analyzer (not shown). Preferably, the containers  6  marked as unacceptable following the analysis carried out in the analysis station  3  are removed from a station (not shown) located downstream of the analysis station  3  and upstream of the analyzer. 
     In the following, a description will be given regarding the use of the preferred embodiment of the device  1  for the determination of serum indices of a biological sample and, more specifically, of the presence of hemolysis, icterus and lipemia (hereinafter: “HIL”) in that sample. However, this implementation is not to be intended in a limiting sense, since the device  1  can also be used for other types of analyses and determinations to be carried out on biological samples, which provide for the irradiation of the sample with a light radiation and the following detection of the intensity of radiation not absorbed by the sample. 
     In the use of the embodiment shown in  FIGS. 1 to 9 , the container  6 , containing the biological sample on which it is desired to perform the HIL screening, is transported towards the analysis station  3  of the device  1  by the automatic conveyor  5  of the automated transport line  2 . Once arrived at the analysis station  3 , the container  6 , housed by a transport device  20 , is blocked and the LED backlight panel  33  is switched on, allowing the camera  30  to identify the type of container  6 . Thereafter, the backlight panel  33  is turned off and the front illuminator  32  is turned on. The rotation system  7  is then activated. The first cylinder  71  activates the first roller  70  of the rotation system  7 , located at a side of the automatic conveyor  5 . The first roller  70  comes out of its location and pushes the transport device  20  against the second roller  72 , located at the opposite side of the automatic conveyor  5 . At this point, the motor  73  drives the rotation of the belt  74  supported by the two pulleys  75   a  and  75   b,  the second of which is pushed towards the transport device  20  through the action of the second cylinder  76 . In this way the belt  74 , which has elastically stretched, presses against the transport device  20  and causes its rotation. In this way, even the container  6  is rotated around its vertical axis. During the rotation, the camera  30  acquires images of the container  6 , thus identifying the sample volume  60  contained within it (ROI, Region of Interest of the sample) and detecting the presence of the label  600  attached to its surface. Later, the camera  30  sends an information to the electronic controller E according to the acquired images, on the basis of which the electronic controller E controls the rotation system  7  so that it rotates the container  6  so as to arrange the label  600  on the opposite side with respect to the camera  30 . Then, the inspection window  61  of the sample is identified on the surface of the sample placed frontally with respect to the camera  30  in a portion totally free not only from the presence of labels  600 , but also from writing, fingerprints or any other impurity, according to the “good laboratory practice”. Once the container  6  is correctly positioned, the rotation system  7  is blocked and the LED radiation source  50  of the lighting system  4  is switched on, emitting white light, which is filtered through one of the filters  510 ,  511 ,  512 ,  513  of the filter holder wheel  51  and, through the optical coupler  52 , reaches the optical fiber  53 . The four filters  510 ,  511 ,  512  and  513  are applied one at a time to the radiation emitted by the LED image source  50 , thus allowing to obtain radiations with four different wavelengths, respectively equal to 450 nm, 520 nm, 575 nm and 660 nm, with which to irradiate the biological sample through the optical fiber  53 . The filter holder wheel  51  includes an additional black filter  514 , used only for a quality control of the LED light emitted by the second illuminator  50 . The path of the radiation, once directed towards the sample  60 , is outlined in  FIG. 9 . The component  300   a  of the radiation  400  emitted by the lighting system  4  is reflected by the sample volume  60  and returns to the camera  30  of the analysis station  3 . The reflection due to the material of which the container  6  is made is considered negligible. The radiation that is not reflected or absorbed by the sample volume  60  reaches the surface of the container  6  opposite to the second end of the optical fiber  53 , where it undergoes a reflection by the label  600 , generating a second component  300   b  of the radiation  400  which, after having again passed through the sample volume  60 , reaches the camera  30 . The camera  30  detects, therefore, a radiation composed of the two components  300   a  and  300   b,  and can acquire an image of the sample volume  60  at the same time as the illumination thereof. 
     Since the analysis is carried out by selecting in sequence 4 different wavelengths (450 nm, 520 nm, 575 nm and 660 nm) from the radiation emitted by the image source  50  by means of the filter holder wheel  51 , the camera  30  acquires a series of images related to these wavelengths. The camera  30  is color, i.e. it is equipped with sensors, each of which sensitive to an area of the visible spectrum corresponding to the four wavelengths used. Each lighting corresponds to a specific color signal. More specifically, 450 nm correspond to a blue signal, 520 nm to a green signal, 570 nm to a yellowish signal and 660 nm to a red signal. In this way it is possible to distinguish the response of the camera  30  on each of the color channels. The camera  30  provides a result, for each of the acquired images, expressed in terms of grey levels of the image, from “255” (very intense signal tending to white) up to “0” (dark signal, tending to black). A grey level response is therefore obtained for each of the above mentioned colored channels; each grey level is given by the sum of the two signal components  300   a,  reflected by the sample volume  60 , and  300   b,  reflected by the label  600 . The ratio between the grey level values, corresponding to the respective light intensities, for two of the wavelengths of interest, gives a non-dimensional number, shown in ordinate in the graph represented in  FIG. 12 , referring to an hemolysis analysis. The symbols in the graph represent each individual serum sample examined. For each of them, the ordinate value represents the ratio between the intensity (detected by the camera  30 ) of the signal at the reference wavelength (660 nm) and the intensity at the absorption wavelength (575 nm). The higher the ordinate value is, the greater is the absorption of the light signal at the chosen absorption wavelength, indicating that the sample is hemolytic. The abscissa value represents the actual hemolysis value (in mg/dL) detected on the same samples by a laboratory analyzer taken as reference. It is to be understood that, for the purpose of assessing whether or not the biological sample is hemolytic, the ratio between the detected intensities of the reference I(ref) and absorption I(abs) radiations can be carried out in any order, that is both I(abs)/I(ref) and I(ref)/I(abs). In the first case, the smaller the value, the more the sample is hemolytic. In the second case, the higher the value, the more the sample is hemolytic. 
     In  FIG. 13  it is shown again the graph represented in  FIG. 12  with four highlighted areas, which allow to perform a comparison between the values detected by the device  1  object of the invention and those detected by the reference laboratory analyzer.  FIG. 13  shows an analysis in classes of a kind in use in many laboratories, i.e. with classes on hemolysis that establish a class 0 for the range from 0 to 50 mg/dl, a class 1 for the range between 50 and 200 mg/dl, and a class 2 for the range above 200 mg/dl. 
     As can be seen, there are few cases in which the samples have been underestimated (“false negatives”, quarter II), that is samples classified by the device  1  as “little” hemolytic that have a high real H value, and there are just as few cases in which they have been overestimated (“false positives”, quarter IV), that is samples classified by the device  1  as “very” hemolytic which have a low real H value. The measurements in quarters I and III (as can be seen, definitely the majority) are instead the correct ones, in which the sample detected by the device as “hemolytic” (quarter III) or “non-hemolytic” (quarter I) is actually such. This also depends, of course, on thresholds that are established to distinguish a sample as “little hemolytic”, “hemolytic” and “very hemolytic”. These thresholds can be arbitrary and vary for each laboratory. In this way there is also the possibility of discriminating the samples by “classes”, dividing them according to different intervals to establish their level of H, on the basis of the same division at intervals that often also the analyzers apply. By analyzing the grey dashes of the graph represented in  FIG. 12 , it is possible to arrive to an estimate and assume that the samples with an ordinate value lower than 3,2 have an H value between 0 and 50, those with a value between 3,2 and 12 have an H value between 50 and 200 and those with a value greater than 12 have an H value greater than 200. 
     The scope is substantially identical for the use of device  1  in an analysis of different serum indices of the biological sample, for example an analysis of icterus levels ( FIG. 14 ) or lipemia ( FIG. 15 ). 
     The samples that are identified as unacceptable following the screening performed in the analysis station  3  are removed from the automated transport line  2  by means of a system arranged for this purpose (not shown), located downstream of the analysis station  3  and upstream of the analyzer, in order to prevent the performance of analyses on samples determined as unsuitable. 
     As it is clear from the above description, the device according to the invention is characterized by greater accuracy and precision of analysis than the currently known devices for the performance of the screening of a biological sample. The positioning of the biological sample container, prior to the screening, in order to exploit the label attached on its surface to reflect the radiation component not absorbed by the sample towards the camera or video camera, advantageously placed on the same side of the analysis source with respect to the container, allows to limit the error that arises when working in transmission and the radiation must pass through the label before being detected by the camera. 
     Studies and experiences carried out by the Applicant have shown that the use of a filter holder device that enables to select multiple different filters and, consequently, as many wavelengths during the same analysis allows to perform, in a single screening, the detection of several different parameters, significantly speeding up the procedures compared to the currently known devices. 
     Of course, without prejudice to the principle of the invention, the construction details and the embodiments may vary widely with respect to what is described and illustrated purely by way of example, without thereby departing from the scope of protection of the present invention, as defined in the annexed claims.