CN116106368A - Blood cell voltage signal processing method and system - Google Patents

Abstract

The invention discloses a blood cell voltage signal processing method and system, and relates to the field of signal identification. The method comprises the following steps: a continuous voltage value of the blood cell signal is obtained in advance, and the continuous voltage signal is obtained according to the continuous voltage value; acquiring a first continuous voltage signal containing a blood cell signal according to a voltage value in the continuous voltage signal; removing false signals in the first continuous voltage signals to obtain second continuous voltage signals; the second continuous voltage signal is subjected to interference optimization processing to obtain a target voltage signal, and the blood cells of the laser beam are used for obtaining an electric signal waveform.

Description

Blood cell voltage signal processing method and system

Technical Field

The invention relates to the field of signal identification, in particular to a blood cell voltage signal processing method and system.

Background

The analysis of blood cells is one of the very wide technologies applied in the clinical laboratory of medical science, and along with the technical development of the medical field, finer analysis requirements are continuously put forward for the key links of blood cell measurement and identification, and the analysis result provides great help for diagnosis made by medical professionals. The optical scattering method is the most common detection principle, so an advanced algorithm is needed to meet the requirement of accurately identifying the signals generated in all directions by optical blood cells.

The accuracy of cell analysis has great influence on the test result, and in a blood sample, the blood sample consists of a plurality of cell groups with different volume sizes and different internal structures, when blood cells passing through a laser beam with specific calibration, scattered light or fluorescence is generated at multiple angles, the forward angle scattered light can effectively reflect the volume of the cells, and the medium-high angle scattered light can detect the internal structures (granularity and inner core split condition) of the cells.

When blood cells subjected to specific calibration pass through the laser beam, waveform signals are formed; in practical applications, there are various factors that may cause interference to the waveform signal, increasing difficulty in recognition and analysis of the signal, for example: circuit noise, flow fluctuations, multiple cell adhesions, bubbles like blood cells, etc.

Disclosure of Invention

The invention aims to solve the technical problem of providing a blood cell voltage signal processing method and system aiming at the defects of the prior art.

The technical scheme for solving the technical problems is as follows:

a method of processing a blood cell voltage signal, comprising:

a continuous voltage value of the blood cell signal is obtained in advance, and the continuous voltage signal is obtained according to the continuous voltage value;

acquiring a first continuous voltage signal containing a blood cell signal according to a voltage value in the continuous voltage signal;

removing false signals in the first continuous voltage signals to obtain second continuous voltage signals;

and performing interference optimization processing on the second continuous voltage signal to obtain a target voltage signal.

The beneficial effects of the invention are as follows: the electrical signal waveform is obtained through the blood cells of the laser beam, and various noises and interferences can be eliminated by adopting the signal recognition algorithm disclosed by the invention, so that the accurate analysis of the optical blood cell signals is realized.

Further, the rejecting the glitch in the first continuous voltage signal specifically includes:

judging whether the first continuous voltage signal meets a preset condition or not;

and eliminating the part of the first continuous voltage signal which does not meet the preset condition.

Further, the preset conditions include:

the width value of the first continuous voltage signal is within a preset range, and no double peak phenomenon occurs.

Further, the performing interference optimization processing on the second continuous voltage signal specifically includes:

and carrying out digital filtering processing and dead zone region removing processing on the second continuous voltage signal.

Further, the method further comprises the following steps:

and carrying out mask processing on the target voltage signal according to application requirements.

Further, the method further comprises the following steps: and obtaining the area value or the amplitude of the target voltage signal according to the application requirement and the target voltage signal.

The other technical scheme for solving the technical problems is as follows:

a system for processing a blood cell voltage signal, comprising: the device comprises a voltage signal acquisition module, a screening module, a rejecting module and an optimizing module;

the voltage signal acquisition module is used for obtaining continuous voltage values of blood cell signals in advance and obtaining continuous voltage signals according to the continuous voltage values;

the screening module is used for acquiring a first continuous voltage signal containing blood cell signals according to the voltage value in the continuous voltage signals;

the rejecting module is used for rejecting false signals in the first continuous voltage signal to obtain a second continuous voltage signal;

the optimizing module is used for carrying out interference optimizing processing on the second continuous voltage signal to obtain a target voltage signal.

The beneficial effects of the invention are as follows: the electrical signal waveform is obtained through the blood cells of the laser beam, and various noises and interferences can be eliminated by adopting the signal recognition algorithm disclosed by the invention, so that the accurate analysis of the optical blood cell signals is realized.

Further, the rejection module is configured to determine whether the first continuous voltage signal meets a preset condition;

and eliminating the part of the first continuous voltage signal which does not meet the preset condition.

Further, the preset conditions include:

the width value of the first continuous voltage signal is within a preset range, and no double peak phenomenon occurs.

Further, the optimization module is specifically configured to perform digital filtering processing and dead zone region rejection processing on the second continuous voltage signal.

Further, the method further comprises the following steps: and the mask processing module is used for carrying out mask processing on the target voltage signal according to application requirements.

Further, the method further comprises the following steps: and the parameter acquisition module is used for acquiring the area value or the amplitude of the target voltage signal according to the application requirement and the target voltage signal.

Additional aspects of the invention will be set forth in part in the description which follows and, in part, will be obvious from the description, or may be learned by practice of the invention.

Drawings

Fig. 1 is a schematic flow chart of a method for processing a blood cell voltage signal according to an embodiment of the present invention;

FIG. 2 is a block diagram of a blood cell voltage signal processing system according to an embodiment of the present invention;

FIG. 3 is a flow chart of baseline calculation provided by other embodiments of the present invention;

FIG. 4 is a signal mask output flow chart provided by other embodiments of the present invention;

fig. 5 is a flowchart of signal parameter calculation according to other embodiments of the present invention.

Detailed Description

The principles and features of the present invention are described below with reference to the drawings, the illustrated embodiments are provided for illustration only and are not intended to limit the scope of the present invention.

As shown in fig. 1, a method for processing a blood cell voltage signal according to an embodiment of the present invention includes:

s1, obtaining a continuous voltage value of a blood cell signal in advance, and obtaining the continuous voltage signal according to the continuous voltage value; from the standpoint of signal sampling and feature extraction, the required ADC sampling rate and number of bits are confirmed. And judging the start-stop control of the algorithm according to whether the measurement analysis is started or not. For example: according to the sample flow rate of blood cells, the light spot area and the pulse condition of various blood cells passing through laser beams, the sample flow rate of the ADC is used as a main factor for selecting the sampling rate of the ADC; and evaluating the dynamic range according to the presentation and analysis of the strong and weak signals in the same graph, and taking the dynamic range as a main factor for selecting ADC digit. And judging that when the laser is enabled, indicating that the analysis of blood cells is started, starting algorithm execution, and continuously acquiring by the ADC to obtain a continuous voltage signal.

S2, acquiring a first continuous voltage signal containing blood cell signals according to the voltage value in the continuous voltage signal;

it should be noted that, the value obtained by the baseline acquisition part in the algorithm is used as a reference for identifying and analyzing the blood cell signals, and when the acquired voltage value is between the preset signal start identification threshold value and the signal end identification threshold value, a tentative signal which is considered as the blood cells is initially acquired.

S3, removing false signals in the first continuous voltage signals to obtain second continuous voltage signals;

it is to be noted that, when the acquired voltage value is higher than the preset signal starting identification threshold, the signal width is synchronously recorded, if the width is smaller than 1us or the width is larger than 3us, the signal identified this time is a false signal and needs to be removed; after the signal satisfying the width range passes, the dead time of the signal is within 2us, and if the signal is recognized again within 2-3 us, the phenomenon of double peaks is shown.

It should be noted that, judging whether the first continuous voltage signal meets a preset condition; the width value of the first continuous voltage signal is within a preset range, and no double peak phenomenon occurs. Wherein the bimodal phenomenon means that in the dead zone region after the end of the signal, if the pulse signal appears again at this time or immediately after the end of the dead zone, the bimodal phenomenon caused by the adhesion of adjacent blood cells appears. The preset range may be that the width of the signal is required to be in the range of 1-3 us.

And eliminating the part of the first continuous voltage signal which does not meet the preset condition.

S4, performing interference elimination optimization processing on the second continuous voltage signal to obtain a target voltage signal. It should be noted that, the interference noise is removed by using a digital filtering method, and an effective signal is obtained by adding a link of removing a dead zone.

The electrical signal waveform is obtained through the blood cells of the laser beam, and various noises and interferences can be eliminated by adopting the signal recognition algorithm disclosed by the invention, so that the accurate analysis of the optical blood cell signals is realized.

Optionally, in some embodiments, the rejecting the glitch in the first continuous voltage signal specifically includes:

judging whether the first continuous voltage signal meets a preset condition or not;

and eliminating the part of the first continuous voltage signal which does not meet the preset condition.

Optionally, in some embodiments, the preset condition includes:

the width value of the first continuous voltage signal is within a preset range, and no double peak phenomenon occurs.

Optionally, in some embodiments, the performing interference optimization processing on the second continuous voltage signal specifically includes:

and carrying out digital filtering processing and dead zone region removing processing on the second continuous voltage signal. The digital filter adopts a conventional first-order low-pass digital filtering principle, namely, the output value is determined by the fixed weight of the newly acquired data and the weight of the data after the last filtering together, and the process is carried out by continuous iteration of software.

Optionally, in some embodiments, further comprising:

and carrying out mask processing on the target voltage signal according to application requirements.

Note that the signal mask processing procedure may include: the meaning of mask introduction is: when single or multiple channel signals are acquired simultaneously, the following functions are achieved: 1. and (3) response processing: according to the mask signal, parameter calculation is carried out; 2. and (3) selection processing: selecting a channel or data to be processed according to the mask signal; 3. multichannel logic judgment: realizing signal combination processing of a plurality of channels; 4. the alignment of signals is convenient, namely the alignment of the signal edges of the multiple channels can be realized according to the delay processing of the mask signals output by the multiple channels. After the signals of the blood cells are identified, the effective width of the signals and the dead zone area of the signals are used as mask signals to be output.

Optionally, in some embodiments, further comprising: and obtaining the area value or the amplitude of the target voltage signal according to the application requirement and the target voltage signal.

The area value and the amplitude are characteristic parameters of blood cells, meanwhile, the parameters are used for judging the effectiveness of signals, the area parameter is marked as A, the highest amplitude parameter is marked as H, and the effectiveness requirement is that:

in a certain embodiment, the signal recognition algorithm obtains the electric signal waveform through the blood cells of the laser beam, and various noises and interferences can be eliminated by adopting the signal recognition algorithm, so that the accurate analysis of the optical blood cell signals is realized.

The signal recognition total algorithm is carried out step by step according to the module algorithm, namely the total algorithm consists of the following algorithm modules: signal baseline acquisition, signal mask output, signal interference elimination, signal parameter calculation and signal validity judgment.

The algorithms of the above-mentioned constituent modules are different, but the modules cannot exist independently, and there is a close connection between the partial modules, and each module can use the data obtained by the algorithms of other modules or output related parameters to provide to other modules according to the need besides the algorithm for completing the main functions of each module.

In the algorithm of each module, according to the characteristics of the main functions to be completed, different signal interference and different corresponding interference elimination modes are respectively provided; i.e. the processing algorithms for signal interference rejection, are distributed in the respective functional algorithm modules.

Signal baseline collection, as shown in figure 3, when the laser is enabled, indicates that analysis of blood cells is started, algorithm execution is started, and the ADC performs data collection; judging that when the acquired voltage value is higher than a preset signal initial identification threshold value, synchronously recording the signal width, if the signal width is smaller than 1us or is larger than 3us, indicating that the current identified signal is a false signal, eliminating, and continuously carrying out normal acquisition of baseline data; when judging that the signal meeting the width range is a useful signal, the base line is not acquired at this stage; after the useful signal is finished, the dead time of the signal is within 2us, and the baseline acquisition is not carried out at the stage; and after the dead zone is over, the baseline is collected normally, and digital low-pass filtering processing of a software algorithm is performed.

The baseline is introduced to provide a reference standard for the identification and analysis of blood cell signals, the standard value is designed and set through a circuit system, and the value is obtained by a baseline acquisition part in an algorithm. Wherein the circuitry may be an analog adder. The design settings may include: the baseline is set within the ADC acquisition range first, and in order to obtain a more complete and accurate signal, the baseline should be selected to be as close to the lower limit of the ADC acquisition range as possible.

The signal baseline acquisition algorithm comprises judgment and selection of true and false signals of blood cells, interference elimination of the blood cell signals on baseline data, interference elimination of signal dead zones on the baseline data, normal acquisition of the baseline signals and digital filtering.

The signal mask output, as shown in figure 4, indicates that the analysis of blood cells is started when the laser is enabled, the algorithm execution is started, and the ADC performs data acquisition; collecting and obtaining a voltage value, comparing the voltage value with a preset signal start identification threshold value, indicating that the signal start appears when the voltage value is larger than the threshold value, synchronously recording the signal width, judging before the signal is ended, and indicating that the signal identified this time is a false signal and needs to be removed if the width is smaller than 1us or the width is larger than 3 us; when the signal is lower than the ending judgment threshold value, the signal is judged to be ended, dead zone removing processing is carried out for 2us, if the signal is identified again within 2-3 us, the signal is judged to have double peaks, the signal is abandoned, otherwise, the corresponding mask is output for the normal signal, and the signal mask output flow is ended. 4 pre-judging thresholds are used in a signal mask output algorithm, each numerical value can be set and adjusted, and the initial recognition threshold value, the end judging threshold value and the minimum value and the maximum value of the signal width are adjusted according to the signal to noise ratio of the measuring system;

the function of the signal-initiated recognition threshold is to recognize whether a blood cell signal is present; the function of the judging threshold value for ending the signal is to identify whether the blood cell signal is ended; the function of predicting the minimum value of the signal width according to the characteristics of the signal is to meet the lower limit value of the signal width of the normal blood cells; the function of predicting the maximum value of the signal width based on the characteristics of the signal is to prevent the normal blood cell signal width from exceeding the upper limit value.

The width counting starts after the signal is acquired, the dead zone area after the signal is ended is not used as the effective width, but if the pulse signal appears again at the moment or just after the dead zone is ended, the double peak phenomenon caused by blood cell adhesion appears. And after the dead zone is over, discarding according to the width of the acquired signal and whether the double peak condition exists.

Signal interference rejection. Except the above mentioned baseline filtering, baseline de-signaling, dead zone processing, double peaks and judgment and disjunction of signals, when the width in signal identification exceeds the design requirement, the abnormal situation is considered, and the abnormal situation is not taken as a normal signal and needs to be removed; wherein, the design requirement signal width is in the range of 1-3 us.

After various interferences are eliminated, the mask waveforms of the blood cell signals are synchronously output, when signals of a plurality of channels are acquired, the algorithms are executed in corresponding quantity, the mask is used, the mask is a digital quantity output in the algorithm, and the digital quantity can be directly output to related different channels by the algorithm in a soft mode or can be mapped to corresponding device pins for output by a hard circuit. 1 indicates normal blood cell signals, 0 indicates no signals, and the mask waveform represents the width occupied by normal signals, and is used as an aid for calculating other parameters or as a basis for logically combining and collecting multichannel signals.

Signal parameter calculation, as shown in fig. 5, when the laser is enabled, the analysis of blood cells is started, algorithm execution is started, and the ADC performs data acquisition; judging a mask signal, continuously collecting the amplitude values of each point of the signal in the mask signal process, accumulating the amplitude values, judging the amplitude value collected each time, and updating and storing the maximum value in the signal; in the process, the width analysis is carried out simultaneously; after the mask signal is finished, judging according to the result of the width analysis, when the signal width is in the range of 1-3 us, the signal is a normal signal, otherwise, the signal is an invalid signal, and directly ending the parameter calculation flow; continuously performing parameter calculation on the effective signals, marking the accumulated result of the amplitude values as A parameters, marking the maximum value of the signals as H parameters, and performing ratio calculation on 2 parameters to obtain another characteristic parameter of blood cells; and outputting the obtained data to the FIFO, latching, and ending the signal parameter calculation flow. All characteristic parameters of the signal can be obtained in the algorithm module, including the signal electric signal parameters and corresponding time axis data. In general, the most important is to acquire the amplitude of the signal. The characteristic parameters can be signal area, height or width, etc.

In the process of identifying the signal, data acquisition is carried out, the amplitude corresponding to the signal can be acquired at each time point, the maximum value of the signal and the time point when the signal appears can be acquired, and the baseline data are used in the calculation of the amplitude. The area parameter of the signal can be obtained through the amplitude of each point of the signal, or other calculation parameters such as the ratio of the area to the maximum amplitude can be indirectly obtained, and the ratio is also a characteristic parameter of blood cells.

And (3) analyzing the pulse width of the signal while calculating the amplitude, and mainly recording the width of the signal larger than the end judgment threshold value and the width of the complete signal respectively.

And judging the validity of the signal. Before the parameters are formally output to the FIFO, checking and analyzing the pulse width data and the required range, and identifying the signal effectiveness; for example: if the signal is within the range of 1-3 us, the signal is invalid when the signal is out of the range. Discarding the signal when the judging result is invalid, and outputting a mark signal when the judging result is valid. This flag signal indicates that the current data is ready for latching into the FIFO.

The method is suitable for recognizing signals generated by blood cells through light beams and by emitting scattered light by the cells, has high recognition rate, can recognize normal blood cell signals, can determine the choice of collected signals according to the size of the blood cells, can distinguish abnormal conditions of adhesion of arranged blood cells and similar blood cell bubbles, is used for eliminating interference factors in recognition, acquires effective signals and avoids the problem of misjudgment.

In one embodiment, a system for processing a blood cell voltage signal includes: a voltage signal acquisition module 1101, a screening module 1102, a rejection module 1103 and an optimization module 1104;

the voltage signal acquisition module 1101 is configured to obtain a continuous voltage value of a blood cell signal in advance, and obtain a continuous voltage signal according to the continuous voltage value;

the screening module 1102 is configured to obtain a first continuous voltage signal including a blood cell signal according to a voltage value in the continuous voltage signal;

the rejecting module 1103 is configured to reject the false signal in the first continuous voltage signal to obtain a second continuous voltage signal;

the optimizing module 1104 is configured to perform interference optimization processing on the second continuous voltage signal to obtain a target voltage signal.

The electrical signal waveform is obtained through the blood cells of the laser beam, and various noises and interferences can be eliminated by adopting the signal recognition algorithm disclosed by the invention, so that the accurate analysis of the optical blood cell signals is realized.

Optionally, in some embodiments, the rejection module 1103 is configured to determine whether the first continuous voltage signal meets a preset condition;

and eliminating the part of the first continuous voltage signal which does not meet the preset condition.

Optionally, in some embodiments, the preset condition includes:

the width value of the first continuous voltage signal is within a preset range, and no double peak phenomenon occurs.

Optionally, in some embodiments, the optimizing module 1104 is specifically configured to perform a digital filtering process and a dead zone region rejection process on the second continuous voltage signal.

Optionally, in some embodiments, further comprising: and the mask processing module is used for carrying out mask processing on the target voltage signal according to application requirements.

Optionally, in some embodiments, further comprising: and the parameter acquisition module is used for acquiring the area value or the amplitude of the target voltage signal according to the application requirement and the target voltage signal.

It is to be understood that in some embodiments, some or all of the alternatives described in the various embodiments above may be included.

It should be noted that, the foregoing embodiments are product embodiments corresponding to the previous method embodiments, and the description of each optional implementation manner in the product embodiments may refer to the corresponding description in the foregoing method embodiments, which is not repeated herein.

In one embodiment, when the laser is enabled, it is determined that the analysis of blood cells is started, the algorithm is started, and the ADC performs continuous acquisition to obtain continuous voltage signals.

The signal is required to be identified according to a preset threshold value of the baseline in the baseline acquisition algorithm, the preset threshold value of the baseline comprises a start judgment threshold value and an end judgment threshold value of the signal occurrence, and the effective benefits of adopting the 2 threshold value data are as follows: distinguishing the floating of the baseline signal from the real signal, and indicating that the real blood cell signal is future if the acquired signal does not reach the initial judgment threshold value, wherein the obtained data is the baseline signal. The acquisition of baseline data, which cannot be acquired when a signal occurs, requires de-signal processing.

In the signal judging process, when a false signal is found, for example, the signal width exceeds the range of 1-3 us, the baseline data can be normally acquired; after the signal passes, a dead zone area with a section is formed, and the data cannot be used as baseline data and needs to be removed; specifically, after the signal end threshold is determined, a certain time is left, and a dead zone of the signal, for example, a time of 2us, may be reserved. The acquired baseline data is subjected to the necessary filtering to remove circuit or system noise, such as digital low pass filtering using software algorithms.

Providing a reliable reference baseline for the identification and analysis of blood cell signals.

The signal mask algorithm uses 4 pre-judging thresholds, and each numerical value can be set and adjusted to be respectively a signal start identification threshold, a signal end judging threshold, a minimum value and a maximum value of a pre-judging signal width; note that the signal predetermined threshold for the start and end of the signal here is the absolute value of the signal amplitude after the baseline data is removed, and its use and value are different from the baseline predetermined threshold at the time of baseline acquisition. The meaning of mask introduction is: when single or multiple channel signals are acquired simultaneously, the following functions are achieved: 1. and (3) response processing: according to the mask signal, parameter calculation is carried out; 2. and (3) selection processing: selecting a channel or data to be processed according to the mask signal; 3. multichannel logic judgment: realizing signal combination processing of a plurality of channels; 4. the alignment of signals is convenient, namely the alignment of the signal edges of the multiple channels can be realized according to the delay processing of the mask signals output by the multiple channels. After the signals of the blood cells are identified, the effective width of the signals and the dead zone area of the signals are used as mask signals to be output.

After the signal amplitude is larger than the recognition threshold value of signal start, the counting of signal width is started, and accumulation is carried out all the time in the effective signal stage, wherein the effective signal stage is the stage in which the signal amplitude is larger than the judgment threshold value of signal end in the width counting process.

The dead zone area after the signal is finished is not used as an effective width, and dead zone removal processing is needed; however, if the pulse signal appears again at this time or immediately after the dead zone is finished, it indicates that a bimodal phenomenon due to the adhesion of adjacent blood cells occurs.

And after the signal dead zone stage is finished, judging whether the signal dead zone stage is broken or not according to the width of the acquired signal and whether the signal dead zone stage is bimodal or not and the design requirement.

For the obtained effective signals, the mask waveform of the blood cell signals is synchronously input while the signal width is obtained, 1 indicates that the normal blood cell signals exist, and 0 indicates that no signals exist.

The mask waveform is used for representing normal signals, the width of the mask is also the width of the signals, and the mask waveform is used as the aid of parameter calculation or as the basis for the logic combination acquisition of multichannel signals, so that the signal identification process of other modules is simplified.

And carrying out data acquisition according to mask waveforms synchronously output in the accumulating process of the width, and obtaining the amplitude value corresponding to each time point signal.

The calculation of the signal amplitude uses the baseline data described above. In the effective process of the signal, the amplitude values of all points of the signal are continuously collected, the amplitude values are accumulated and calculated, meanwhile, the amplitude value collected each time is judged, and the maximum value in the signal is updated and stored.

And (3) analyzing the pulse width of the signal while calculating the amplitude, and mainly recording the width of the signal larger than the end judgment threshold value and the width of the complete signal respectively.

After the mask waveform is finished, the complete amplitude of each point of the signal, including the maximum value, can also be obtained according to the data requirement, or the area value of the signal can be obtained, or other calculation can be carried out.

The signal effectiveness judgment is mainly carried out according to the result of signal width analysis; when the signal width is in the range of 1-3 us, the signal is a normal signal, otherwise, the signal is an invalid signal. When the judgment result is invalid, the signal is discarded, and when the judgment result is valid, a flag signal is output, which indicates that the current data is ready for latching in the FIFO.

The beneficial effects of adopting the mode are as follows: can eliminate the interference of blood cell adhesion and abnormal bubble signals and the requirement of fine design identification.

When a series of arranged blood cells pass through the laser beam, the cells emit scattered light at all angles, and the collected signals pass through the algorithm to obtain corresponding series of data, and the corresponding series of data are put into a buffer memory for standby.

The reader will appreciate that in the description of this specification, a description of terms "one embodiment," "some embodiments," "examples," "specific examples," or "some examples," etc., means that a particular feature, structure, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the invention. In this specification, schematic representations of the above terms are not necessarily directed to the same embodiment or example. Furthermore, the particular features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples. Furthermore, the different embodiments or examples described in this specification and the features of the different embodiments or examples may be combined and combined by those skilled in the art without contradiction.

In the several embodiments provided in this application, it should be understood that the disclosed apparatus and method may be implemented in other ways. For example, the method embodiments described above are merely illustrative, e.g., the division of steps is merely a logical function division, and there may be additional divisions of actual implementation, e.g., multiple steps may be combined or integrated into another step, or some features may be omitted or not performed.

The above-described method, if implemented in the form of a software functional unit and sold or used as a stand-alone product, may be stored in a computer-readable storage medium. Based on such understanding, the technical solution of the present invention is essentially or a part contributing to the prior art, or all or part of the technical solution may be embodied in the form of a software product stored in a storage medium, comprising several instructions for causing a computer device (which may be a personal computer, a server, or a network device, etc.) to perform all or part of the steps of the methods of the embodiments of the present invention. And the aforementioned storage medium includes: a usb disk, a removable hard disk, a Read-only memory (ROM), a random access memory (RAM, randomAccessMemory), a magnetic disk, or an optical disk, or other various media capable of storing program codes.

The present invention is not limited to the above embodiments, and various equivalent modifications and substitutions can be easily made by those skilled in the art within the technical scope of the present invention, and these modifications and substitutions are intended to be included in the scope of the present invention. Therefore, the protection scope of the invention is subject to the protection scope of the claims.

Claims (10)

1. A method for processing a blood cell voltage signal, comprising:

a continuous voltage value of the blood cell signal is obtained in advance, and the continuous voltage signal is obtained according to the continuous voltage value;

acquiring a first continuous voltage signal containing a blood cell signal according to a voltage value in the continuous voltage signal;

removing false signals in the first continuous voltage signals to obtain second continuous voltage signals;

and performing interference optimization processing on the second continuous voltage signal to obtain a target voltage signal.

2. The method according to claim 1, wherein the removing the false signal from the first continuous voltage signal comprises:

judging whether the first continuous voltage signal meets a preset condition or not;

and eliminating the part of the first continuous voltage signal which does not meet the preset condition.

3. A method of processing a blood cell voltage signal according to claim 2, wherein the predetermined condition comprises:

the width value of the first continuous voltage signal is within a preset range, and no double peak phenomenon occurs.

4. A method of processing a blood cell voltage signal according to any one of claims 1-3, wherein said performing an interference optimization process on said second continuous voltage signal comprises:

and carrying out digital filtering processing and dead zone region removing processing on the second continuous voltage signal.

5. The method for processing a blood cell voltage signal according to claim 1, further comprising:

and carrying out mask processing on the target voltage signal according to application requirements.

6. The method for processing a blood cell voltage signal according to claim 1, further comprising: and obtaining the area value or the amplitude of the target voltage signal according to the application requirement and the target voltage signal.

7. A system for processing a blood cell voltage signal, comprising: the device comprises a voltage signal acquisition module, a screening module, a rejecting module and an optimizing module;

the voltage signal acquisition module is used for obtaining continuous voltage values of blood cell signals in advance and obtaining continuous voltage signals according to the continuous voltage values;

the screening module is used for acquiring a first continuous voltage signal containing blood cell signals according to the voltage value in the continuous voltage signals;

the rejecting module is used for rejecting false signals in the first continuous voltage signal to obtain a second continuous voltage signal;

the optimizing module is used for carrying out interference optimizing processing on the second continuous voltage signal to obtain a target voltage signal.

8. The system of claim 7, wherein the rejection module is configured to determine whether the first continuous voltage signal meets a predetermined condition;

and eliminating the part of the first continuous voltage signal which does not meet the preset condition.

9. The system for processing a blood cell voltage signal according to claim 8, wherein the preset condition comprises:

the width value of the first continuous voltage signal is within a preset range, and no double peak phenomenon occurs.

10. A blood cell voltage signal processing system according to any one of claims 7-9, wherein the optimization module is specifically configured to perform digital filtering and dead zone region rejection on the second continuous voltage signal.

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