WO2013064035A1 - Procédé et dispositif de débruitage pour signal optique - Google Patents

Procédé et dispositif de débruitage pour signal optique Download PDF

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Publication number
WO2013064035A1
WO2013064035A1 PCT/CN2012/083605 CN2012083605W WO2013064035A1 WO 2013064035 A1 WO2013064035 A1 WO 2013064035A1 CN 2012083605 W CN2012083605 W CN 2012083605W WO 2013064035 A1 WO2013064035 A1 WO 2013064035A1
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pulse
denoising
optical signal
signal
digital
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PCT/CN2012/083605
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English (en)
Chinese (zh)
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代勇
郁琦
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深圳迈瑞生物医疗电子股份有限公司
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Publication of WO2013064035A1 publication Critical patent/WO2013064035A1/fr

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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01D—MEASURING NOT SPECIALLY ADAPTED FOR A SPECIFIC VARIABLE; ARRANGEMENTS FOR MEASURING TWO OR MORE VARIABLES NOT COVERED IN A SINGLE OTHER SUBCLASS; TARIFF METERING APPARATUS; MEASURING OR TESTING NOT OTHERWISE PROVIDED FOR
    • G01D3/00—Indicating or recording apparatus with provision for the special purposes referred to in the subgroups
    • G01D3/028—Indicating or recording apparatus with provision for the special purposes referred to in the subgroups mitigating undesired influences, e.g. temperature, pressure
    • G01D3/032—Indicating or recording apparatus with provision for the special purposes referred to in the subgroups mitigating undesired influences, e.g. temperature, pressure affecting incoming signal, e.g. by averaging; gating undesired signals
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01D—MEASURING NOT SPECIALLY ADAPTED FOR A SPECIFIC VARIABLE; ARRANGEMENTS FOR MEASURING TWO OR MORE VARIABLES NOT COVERED IN A SINGLE OTHER SUBCLASS; TARIFF METERING APPARATUS; MEASURING OR TESTING NOT OTHERWISE PROVIDED FOR
    • G01D5/00—Mechanical means for transferring the output of a sensing member; Means for converting the output of a sensing member to another variable where the form or nature of the sensing member does not constrain the means for converting; Transducers not specially adapted for a specific variable
    • G01D5/26—Mechanical means for transferring the output of a sensing member; Means for converting the output of a sensing member to another variable where the form or nature of the sensing member does not constrain the means for converting; Transducers not specially adapted for a specific variable characterised by optical transfer means, i.e. using infrared, visible, or ultraviolet light

Definitions

  • the present invention relates to the field of data processing, and in particular, to a method and apparatus for denoising an optical signal.
  • fluorescent and scatter signals are extracted for identification and analysis of various blood cells.
  • the fluorescence signal is very weak and is easily interfered by various factors, such as background noise, electrical noise, non-specific fluorescent signals, etc. (the so-called non-specific fluorescent signal is relative to the fluorescent signal emitted by the substance to be tested, it is other substances in the blood.
  • the resulting fluorescent signal also known as noise, has a significant impact on the accuracy of fluorescence signal analysis.
  • the signal generated by platelets is weak, and the influence of noise and interference signals is particularly serious.
  • scattered signals can also be affected by noise.
  • a method for denoising an optical signal takes an optical signal as an example, and includes the following steps:
  • Step S01 receiving an optical signal to generate an analog optical pulse signal
  • Step S02 converting the optical pulse signal into a digital optical signal
  • Step S03 acquiring at least two types of pulse characteristic information of each pulse in the digital optical signal
  • Step S04 generating a scattergram of the digital optical signal of two or more dimensions with the at least two kinds of pulse characteristic information as coordinate axes;
  • Step S05 according to the feature that the effective data point and the noise data point distribution area in the scattergram of the digital optical signal are relatively separated, the pulse data corresponding to the noise data point in the digital optical signal is removed, and an effective optical signal is generated;
  • Step S06 storing the effective optical signal.
  • the step S05 is to remove pulse data in the digital light signal corresponding to the preset denoising template according to the preset denoising template; the denoising template is The scatter plot of the digital light signal corresponds to a two-dimensional or two-dimensional boundary region having a boundary value corresponding to the noise data point distribution region.
  • the preset denoising templates have at least two, corresponding to the background detection mode and the blood sample detection mode.
  • the step S05 includes the following steps:
  • Denoising is performed by calling the corresponding denoising template according to the first mode signal and the second mode signal.
  • the at least two kinds of pulse characteristic information are a two-two combination or a three-three combination in a peak, a relative peak, a pulse width, a pulse area, a pulse generation time, and a pulse interval time.
  • the pulse characteristic information acquired in the step S03 includes a relative peak value and a pulse width; and the step S04 is to generate the two-dimensional digital light signal with the relative peak value and the pulse width as coordinate axes. Scatter plot.
  • the step S05 includes the following steps:
  • the pulse data corresponding to the data points in the smaller distribution area is removed.
  • the optical signal is a fluorescent signal.
  • a denoising device for an optical signal comprising: a photosensor for receiving an optical signal to generate an analog optical pulse signal; and an analog to digital conversion circuit for using the simulated light The pulse signal is converted into a digital optical signal; the denoising device of the optical signal further comprises: a pulse extraction module, a pulse information combination module, a denoising module and a storage module,
  • the pulse extraction module is configured to acquire at least two types of pulse characteristic information of each pulse in the digital optical signal
  • the pulse information combination module is configured to generate a scattergram of the digital optical signal of two or more dimensions with at least two kinds of pulse characteristic information as coordinate axes;
  • the denoising module is configured to remove pulse data corresponding to the noise data point in the digital optical signal according to a feature that the effective data point and the noise data point distribution area in the scattergram of the digital optical signal are relatively separated, and generate effective light. signal;
  • the storage module is configured to store the effective optical signal.
  • the denoising module includes: a denoising template memory and a denoising unit, wherein the denoising template memory is configured to store at least one preset corresponding to a scattergram of the digital optical signal a two-dimensional or two-dimensional denoising template having a boundary value corresponding to the noise data point distribution area; the denoising unit is configured to invoke the denoising template in the denoising template memory to remove the The pulse data in the region corresponding to the denoising template in the digital optical signal.
  • At least two types of the denoising templates are preset in the denoising template memory, corresponding to the background detection mode and the blood sample detection mode.
  • the denoising module further includes: a pulse information statistic unit and a comparison unit, wherein the pulse information statistic unit is configured to analyze and obtain data in a preset range in the scattergram of the digital optical signal. The number of points;
  • the comparing unit is configured to compare the quantity value with a preset value, and when it is less than the preset value, determine that the background detecting mode outputs a first mode signal, when the preset value is greater than or equal to the preset value. Determining that the blood sample detection mode outputs a second mode signal;
  • the denoising unit is configured to invoke the corresponding denoising template in the denoising template memory according to the first mode signal and the second mode signal, and remove the denoising template from the digital optical signal. Corresponding to the pulse data in the area.
  • the denoising module includes: an image recognition unit and a noise processing unit, wherein the image recognition unit is configured to identify one large and one small data points in the scattergram of the digital light signal a distribution area; the noise processing unit is configured to remove pulse data corresponding to data points in the smaller distribution area.
  • the at least two kinds of pulse characteristic information acquired by the pulse extraction module are two or two combinations in a peak, a relative peak, a pulse width, a pulse area, a pulse generation time, and a pulse interval time. Three or three combinations.
  • the pulse extraction module includes: a pulse identification unit, a peak buffer, a baseline buffer, a pulse width buffer, and a relative peak calculation unit.
  • the pulse identification unit is configured to acquire peak information, baseline information, and pulse width information of each pulse in the digital optical signal, and store the information in the peak buffer, the baseline buffer, and the pulse width buffer, respectively. ;
  • the relative peak calculating unit is configured to calculate relative peak information according to the peak information in the peak buffer and the baseline buffer and the baseline information;
  • the pulse information combining module is configured to generate a scattergram of the two-dimensional digital light signals with relative peaks and pulse widths as coordinate axes.
  • the optical signal is a fluorescent signal.
  • the above method and device for denoising an optical signal are effective data points and noises in a multi-dimensional (two-dimensional and above) scattergram composed of a plurality of (two or more) pulse characteristic information of a digital optical signal obtained by experimental research.
  • the data point distribution area is relatively separated, and the two-dimensional or multi-dimensional denoising is performed.
  • the traditional technology only uses a single threshold filtering method (ie, horizontal/vertical one-cutting method) to denoise, and the denoising effect is that either more noise signals can be removed or more effective data can be removed. .
  • the optical signal denoising method and device of the present invention can achieve better denoising effect, thereby making the subsequent detection result more accurate.
  • FIG. 1 is a flow chart showing the steps of a method for denoising an optical signal according to an embodiment
  • FIG. 2 is a schematic diagram of a two-dimensional scattergram of a digital fluorescent signal
  • FIG. 3 is a schematic diagram of a denoising template corresponding to a two-dimensional scattergram of the digital fluorescent signal shown in FIG. 2;
  • Figure 4 is a two-dimensional scatter plot of the digital fluorescent signal and the digital scattered signal of the background before denoising
  • Figure 5 is a two-dimensional scatter plot of the digital fluorescent signal and the digital scattered signal of the background after denoising
  • Figure 6 is a two-dimensional scatter plot of the digital fluorescent signal and the digital scattered signal of the blood sample before denoising
  • FIG. 8 is a functional block diagram of a denoising device for an optical signal according to an embodiment
  • FIG. 9 is a functional block diagram of a denoising module of another embodiment.
  • FIG. 1 it is a flow chart of a method for denoising an optical signal according to an embodiment, and includes the following steps:
  • step S01 a fluorescent signal is received to generate a simulated fluorescent pulse signal.
  • step S02 the fluorescent pulse signal is converted into a digital fluorescent signal.
  • Step S03 acquiring at least two kinds of pulse characteristic information of each pulse in the digital fluorescent signal.
  • the pulse characteristic information refers to information such as a peak value, a relative peak value, a pulse width, a pulse area, a time at which a pulse is generated, and a time interval at a pulse interval.
  • the relative peak refers to the peak value of the actually obtained peak relative to the baseline of the signal.
  • the at least two kinds of pulse characteristic information acquired in the step S03 may be any two-two combination or three-three combination of the above-mentioned various pulse characteristic information.
  • step S04 a scattergram of two-dimensional or two-dimensional digital fluorescent signals with at least two types of pulse characteristic information as coordinate axes is generated.
  • FIG. 2 it is a schematic diagram of a two-dimensional scattergram of a digital fluorescent signal with a pulse width as a horizontal axis and a relative peak as a vertical axis obtained by experiments.
  • the distribution of data points presents one large and one small two separate data areas: a larger data area 10 and a smaller data area 12.
  • the smaller data area 12 is distributed with noise data points, and the larger data area 10 is distributed with valid data points.
  • the two data areas do not necessarily have the absolute separation as shown in Figure 2, there will be a small part of the adhesion, but basically separated.
  • Step S05 according to the feature that the effective data point and the noise data point distribution area in the scattergram of the digital fluorescence signal are relatively separated, the pulse data corresponding to the noise data point in the digital fluorescent signal is removed, and an effective fluorescent signal is generated.
  • the effective fluorescent signal is the denoised digital fluorescent signal.
  • the relative separation refers to: in actual cases, the area where the effective data points and the noise data points are distributed is not absolutely separated, and there is a small part of adhesion, but basically in two separate areas.
  • Step S06 storing the effective fluorescent signal.
  • step S05 is to remove the pulse data corresponding to the noise data points distributed in the smaller data area 12.
  • step S05 is to remove the pulse data corresponding to the noise data points distributed in the smaller data area 12.
  • step S05 if denoising is performed by using a preset template, at least one two-dimensional or two-dimensional denoising template having a boundary value corresponding to the scattergram of the digital fluorescent signal may be preset in advance, the boundary. The value corresponds to the noise data point distribution area. Step S05 is to remove the pulse data in the corresponding region of the digital fluorescence signal corresponding to the preset denoising template according to the preset denoising template.
  • two different denoising templates can be preset and used in different situations.
  • the blood cell analyzer includes two types of background detection mode and blood sample detection mode.
  • the background detection mode refers to the empty machine test when the blood sample is not placed to check whether the instrument is clean.
  • the blood sample detection mode refers to the detection mode in which the blood sample to be tested is placed.
  • the preset two different denoising templates respectively correspond to the two detection modes.
  • FIG. 3 it is a schematic diagram of a denoising template corresponding to the two-dimensional scattergram of the digital fluorescent signal shown in FIG. 2.
  • the boundary area 20 and the border area 22 shown in FIG. 3 represent two different denoising templates preset. If denoising according to the boundary region 20, please refer to FIG. 2 at the same time, that is, the data points (corresponding pulse data) in the region corresponding to the boundary region 20 in FIG. 2 are removed, that is, the dotted line 14 and the coordinate axis in FIG. 2 are removed. Data points within a region, and these data points are noise data points.
  • different denoising templates are set for the two detection modes because: the distribution range of the noise data points in the two detection modes obtained according to the experiment is different, and accordingly, corresponding denoising templates are set for different detection modes to achieve More accurate denoising effect.
  • the present invention provides an automatic identification detection mode method, as follows:
  • the preset range may be: a range defined by a relative peak > 512 and a pulse width > 10, and the specific values are obtained experimentally.
  • step S05 comparing the quantity value with the preset value, and when less than the preset value (such as 50), determining the background detection mode, and outputting the first mode signal.
  • the denoising template corresponding to the background detection mode is called according to the first mode signal to perform denoising.
  • the preset value is greater than or equal to, the blood sample detection mode is determined, and the second mode signal is output.
  • Step S05 is to perform denoising according to the demodulation template corresponding to the blood sample detection mode according to the second mode signal.
  • a blood cell analyzer When a blood cell analyzer performs background and blood sample detection, it is usually a two-dimensional scattergram that establishes a digital fluorescent signal and a digital scattered signal to analyze the sample.
  • the digital scatter signal is obtained by analog-to-digital conversion of a forward pulse signal generated by a scatter signal.
  • FIG. 4 and FIG. 5 are two-dimensional scatter plots based on digital fluorescence signals and digital scatter signals before and after denoising in actual background detection.
  • the horizontal axis is the digital fluorescent signal FL and the vertical axis is the digital scatter signal. FSC. It can be clearly seen that there are more data points in the lower left corner of Figure 4, and all data points are noise data points in the background detection.
  • Figure 5 shows the effect of denoising, where the data points are significantly reduced, that is, the noise data is substantially cleared.
  • Figure 6 and Figure 7 are two-dimensional scatter plots based on digital fluorescence signals and digital scatter signals before and after denoising, the horizontal axis is the digital fluorescence signal FL and the vertical axis is the digital scatter signal FSC. .
  • the data points in the box shown in Figure 6 are the corresponding data points of the platelets in the blood sample. It is obvious that there are a large number of data points on the left side of the box. (Traditionally, the left side of the box is directly placed on this figure. The data points are all "cut off", but doing so will cut off useful platelet signals at the same time, resulting in reduced accuracy of the results) and most of these data points are noise data points.
  • the platelet value obtained by the impedance sample using the impedance method was 0 in the background detection mode and 81 ⁇ 10 9 /L in the blood sample detection mode.
  • the data measured before and after denoising by optical detection are shown in the following table: Before denoising After denoising Optical platelet measurement (10 9 /L) Background detection mode twenty one 1 Optical platelet measurement (10 9 /L) Blood sample detection mode 141 78
  • step S05 is performed by image processing for denoising, the following steps are included:
  • the pulse data corresponding to the data points in the smaller distribution area is then removed.
  • This method does not need to preset the boundary of the fixed data point to be removed, but removes the data in the smaller distribution area by means of image recognition, and the purpose and effect of removing noise can also be achieved.
  • the present invention provides a denoising device for the above-mentioned optical signal denoising method with an optical signal corresponding thereto.
  • FIG. 8 it is a functional block diagram of the optical signal denoising device 30 of an embodiment, including: a photo sensor 301, a signal conditioning circuit 302, an analog to digital conversion circuit 303, a pulse extraction module 304, and a combination of pulse information.
  • the photosensor 301 is configured to receive a fluorescent signal to generate a simulated fluorescent pulse signal.
  • the signal conditioning circuit 302 is configured to amplify, filter, and limit the fluorescent pulse signals.
  • An analog to digital conversion circuit 303 is used to convert the fluorescent pulse signal into a digital fluorescent signal.
  • the pulse extraction module 304 is configured to acquire at least two types of pulse characteristic information of each pulse in the digital fluorescent signal.
  • the pulse characteristic information refers to information such as a peak value, a relative peak value, a pulse width, a pulse area, a timing at which a pulse is generated, and a time interval of a pulse interval.
  • the relative peak refers to the peak value of the actually obtained peak relative to the baseline of the signal.
  • the acquired at least two kinds of pulse characteristic information may be any two-two combination or three-three combination of the various pulse characteristic information enumerated above.
  • the pulse information combination module 305 is configured to generate a scattergram of a two-dimensional or two-dimensional digital fluorescent signal having at least two types of pulse characteristic information as coordinate axes.
  • the denoising module 306 is configured to remove the pulse data corresponding to the noise data points in the digital fluorescent signal according to the characteristics of the relative separation of the effective data points and the noise data point distribution regions in the scattergram of the digital fluorescent signal, to generate an effective fluorescent signal.
  • the storage module 307 is configured to store the effective fluorescent signal.
  • the effective fluorescent signal is the denoised digital fluorescent signal.
  • the pulse extraction module 304 further includes: a pulse identification unit 341, a peak buffer 342, a baseline buffer 343, a pulse width buffer 344, and a relative peak calculation unit 345.
  • the pulse identification unit 341 is configured to acquire peak information, baseline information, and pulse width information of each pulse in the digital fluorescent signal, and store them in the peak buffer 342, the baseline buffer 343, and the pulse width buffer 344, respectively.
  • the relative peak calculation unit 345 is configured to calculate relative peak information based on the peak information and the baseline information in the peak buffer 342 and the baseline buffer 343.
  • the pulse information combining module 305 is used to generate a scattergram of the two-dimensional digital fluorescent signal with the relative peak and pulse width as the coordinate axes.
  • the denoising module 306 further includes: a pulse information counting unit 361, a comparing unit 362, a denoising template memory 363, and a denoising unit 364.
  • the denoising template memory 363 is configured to store at least one predetermined two-dimensional or two-dimensional denoising template having a boundary value corresponding to a scattergram of the digital fluorescent signal, the boundary value corresponding to the noise data point distribution area.
  • the denoising template memory 363 stores two denoising templates corresponding to the background detection mode and the blood sample detection mode.
  • the pulse information statistics unit 361 is configured to analyze the number of data points in the scatter plot of the digital fluorescence signal within a preset range.
  • the preset range may be a range defined by a relative peak > 512 and a pulse width > 10.
  • the comparison unit 362 is configured to compare the quantity value with a preset value, and when less than the preset value (such as 50), determine a background detection mode, and output a first mode signal; when the preset is greater than or equal to the preset When the value is determined, the blood sample detection mode is determined, and the second mode signal is output.
  • a preset value such as 50
  • the denoising unit 364 is configured to invoke a corresponding denoising template in the denoising template memory 363 according to the first mode signal and the second mode signal to remove pulse data in the corresponding region of the digital fluorescence signal and the denoising template.
  • FIG. 9 is a functional block diagram of the denoising module 406 of another embodiment, which includes an image recognition unit 461 and a noise processing unit 462 .
  • the image recognition unit 461 is configured to recognize a large one and a small data point distribution area in the scattergram of the digital fluorescent signal.
  • the present invention proposes the use of image processing to remove noise.
  • the noise processing unit 462 is configured to remove pulse data corresponding to data points in the smaller distribution area.
  • the optical signal denoising method and apparatus of the present invention are multi-dimensional (two-dimensional and above) scatters composed of multiple (two or more) pulse characteristic information of the digital fluorescent signal obtained by experimental research.
  • the effective data points and the noise data point distribution areas are relatively separated, and the two-dimensional or multi-dimensional denoising is performed. That is, after the multi-dimensional scattergram of the digital fluorescent signal is established, the noise data can be conveniently and accurately removed, such as the preset denoising template method and image processing method provided in the present case.
  • the traditional technology only uses a single threshold filtering method (ie, horizontal/vertical one-cutting method) to denoise, and the denoising effect is that either more noise signals can be removed or more effective data can be removed. .
  • the optical signal denoising method and device of the present invention can achieve better denoising effect, thereby making the subsequent detection result more accurate.
  • the above method and device for denoising the optical signal are only exemplified by the fluorescent signal, and other optical signals, how to scatter the signal, etc., can be denoised by using the denoising method and device of the above optical signal.

Abstract

La présente invention porte sur un procédé de débruitage pour signal optique, comprenant : réception d'un signal optique et génération d'un signal d'impulsion optique simulé (S01) ; conversion du signal d'impulsion optique en un signal optique numérique (S02) ; acquisition d'au moins deux genres d'informations caractéristiques d'impulsion de chaque impulsion dans le signal optique numérique (S03) ; génération d'un diagramme de dispersion 2D ou plus que 2D pour le signal optique numérique prenant les au moins deux genres d'informations caractéristiques d'impulsion en tant qu'axe de coordonnées (S04) ; retrait des données d'impulsion correspondant à un point de données de bruit dans le signal optique numérique selon la caractéristique que la zone de distribution des points de données valides et celles des points numériques de bruit sont séparées de manière relative dans le diagramme de dispersion du signal optique numérique et génération d'un signal optique valide (S05) ; et stockage du signal optique valide (S06). La présente invention porte également sur un dispositif de débruitage correspondant pour signal optique. Le procédé et le dispositif de débruitage pour signal optique emploient un débruitage multidimensionnel, et au moyen d'une vérification d'expérimentation, telle que comparée à l'état de la technique, le procédé et le dispositif de débruitage pour signal optique peuvent atteindre de meilleurs effets de débruitage, rendant ainsi les résultats de détection ultérieurs plus précis.
PCT/CN2012/083605 2011-10-31 2012-10-26 Procédé et dispositif de débruitage pour signal optique WO2013064035A1 (fr)

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