CN108113664B - Method and system for inhibiting ringing of notch filter in electrocardiosignal acquisition process - Google Patents
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Abstract
A method and a system for inhibiting the ringing of a notch filter in the electrocardiosignal acquisition process are provided, which are used for sampling the electrocardiosignal in real time to acquire the electrocardiosignal, and the method comprises the following steps: the method comprises a caching step, a large-amplitude mutation signal detection and suppression step, a small-amplitude mutation signal detection step, a notching step and a caching moment determination step. The method and the system provided by the embodiment of the invention have the advantages of high calculation efficiency, simple and convenient implementation and strong applicability.
Description
Technical Field
The invention belongs to the technical field of electrocardiosignal processing, and particularly relates to a method and a system for inhibiting ringing of a notch filter in an electrocardiosignal acquisition process.
Background
In each cardiac cycle, the heart can be recorded by an Electrocardiograph (ECG) signal, the heart is excited by a pacing point, an atrium and a ventricle in each cardiac cycle, and the bioelectricity change is accompanied, namely the electrocardiograph, and the form change of the bioelectricity reflects the heart function of a human body and is a reference basis for reflecting the heart state.
In the prior art, an electrocardiosignal of a human body is acquired by using an electrocardio detector, interference signals doped during detection such as baseline drift, power frequency interference, myoelectric interference and the like are removed by a filtering method, a clearer electrocardiosignal is obtained, and then characteristics such as a QRS wave, an RR interval, an S wave, a T wave, ST segment displacement, an ST segment slope and the like of the electrocardiosignal are extracted by adopting a characteristic extraction method so as to reflect the strength of the heart function. The amplitude of the electrocardiosignal is in the range of about 10 μ V to about 5mV, and the frequency is in the range of about 0.05 to about 100 Hz. A typical cardiac signal waveform is shown in figure 1.
During cardiac pacing, the rising edge of the original electrocardiosignal is a steep QR wave, and has a sudden change, as shown in FIG. 2, wherein the horizontal axis represents time in milliseconds ms, and the vertical axis represents the intensity of the electrocardiosignal in microvolt μ V. Due to the inherent characteristics of the filter in the electrocardiosignal detecting instrument, the sudden change signal is easy to generate ringing near the inflection point of the R wave after passing through the notch filter, and the acquired electrocardiosignal generating ringing has interference and cannot normally reflect the heart function of a human body as shown in figure 3.
In order to suppress ringing in the collected electrocardiographic signals, adaptive filters or correlation averaging methods are generally adopted, but these methods are complex in calculation and large in calculation amount, and are not suitable for real-time processing of the electrocardiographic signals.
Disclosure of Invention
In order to reduce the operation amount and improve the adaptability of the algorithm in the electrocardiosignal acquisition process, the embodiment of the invention provides a method for inhibiting the ringing of a notch filter in the electrocardiosignal application process, which comprises the following steps:
a caching step: caching the current sampling time tiA plurality of buffer instants t in a previous time period0、t1、...、ti-1Trapped wave output electrocardiosignal d [0 ]]、d[1]、...、d[i-1]Wherein i is a natural number greater than or equal to 2, and the time period has a length of [10ms,30 ms%]Value in the range, the caching time t0、t1、...、ti-1Time t is cached according to time sequencei-1Closest to the current sampling instant ti；
Detecting and inhibiting a large amplitude mutation signal: for the current sampling time tiSampled original electrocardiosignal d0[i]Detecting and inhibiting the great amplitude mutation signal to obtain the current sampling time tiCardiac electric signal d [ i ]]Entering a small-amplitude mutation signal detection step;
detecting a small-amplitude mutation signal: is calculated at time t1、...、ti-1、tiIs the absolute value of the slope | k [ n ] of each electrocardiographic signal]|：
|k[n]|＝|(d[n]-d[n-1])/(tn-tn-1)|，
Where n is 1, if | k [1 ]]|、|k[2]|、...、|k[i-1]The average value of | is less than the threshold value L of the rate of change of the electrocardiosignal per unit time, and | k [ i |)]If | is greater than the threshold value H of the change rate of the electrocardiosignals in unit time, the current sampling time t is judgediCardiac electric signal d [ i ]]Presence of small mutations;
a trapping step: if the current sampling time tiCardiac electric signal d [ i ]]If small sudden change exists, a first filter is adopted for carrying out trapped wave output;
a cache time determining step: if the current sampling time tiCardiac electric signal d [ i ]]If there is no small sudden change, determining the current sampling time tiBelonging to the caching moment;
and returning to the step: and returning to the caching step.
Further, in the step of detecting and inhibiting the large amplitude mutation signal, the current sampling time t is obtainediOf the original cardiac signal d0[i]Previous buffering time ti-1The electrocardiosignal d [ i-1 ]]Calculating the gradient k [ i ] of the electrocardiosignal at the current sampling moment]Comprises the following steps:
k[i]＝(d0[i]-d[i-1])/(ti-ti-1)，
if the slope k [ i ] of the electrocardiosignal at the current sampling moment]Absolute value of | k [ i]If | is greater than the preset electrocardiosignal change threshold value A in unit time, determining the electrocardiosignal at the current sampling moment as a large-amplitude mutation signal, and determining the current sampling moment tiCardiac electric signal d [ i ]]Comprises the following steps:
d[i]＝d[i-1]+(k[i]/|k[i]|)*A；
if the current sampling time tiGradient k [ i ] of electrocardiosignal]Is less than the preset electrocardiosignal change threshold value A of unit time and the current sampling time tiCardiac electric signal d [ i ]]Comprises the following steps: d [ i ]]＝d0[i]。
Further, in the step of detecting and inhibiting the large amplitude mutation signal, the set electrocardiosignal change threshold A per ms takes values in the range of [800 muV, 1200 muV ].
Further, if the current sampling time tiCardiac electric signal d [ i ]]And if the small-amplitude abrupt change does not exist, performing notching output by adopting a first filter in the notching step, wherein the first filter is a filter without a buffer function.
Further, if the current sampling time tiCardiac electric signal d [ i ]]And if the small-amplitude abrupt change does not exist, performing notching output on the small-amplitude abrupt change by adopting a second filter in the notching step.
Further, after the caching step, the method further comprises a time interval judgment step of acquiring the current sampling time tiAnd the previous buffering time ti-1Time interval t betweeni-ti-1If the time interval t isi-ti-1If the set time threshold is exceeded, the second filtering is usedThe device is used for sampling the current sampling time tiOf the original cardiac signal d0[i]Carrying out notch output and determining the current sampling time tiReturning to the caching step at the caching moment to process the electrocardiosignals at the next moment; if the time interval ti-ti-1And if the set time threshold is not exceeded, entering a step of detecting and inhibiting the large-amplitude mutation signal.
Further, in the buffering step, the buffering time period is 16 ms.
Further, the time interval of the electrocardiosignal sampling is equal time interval 2 ms.
Further, the electrocardiosignal change rate threshold value L in unit time takes a value within the range of [10 muV/ms, 30 muV/ms ], and the electrocardiosignal change rate threshold value H in unit time takes a value within the range of [60 muV/ms, 100 muV/ms ].
The embodiment of the invention also provides a system for inhibiting the ringing of the notch filter in the electrocardiosignal acquisition process, which comprises a buffer component, a large-amplitude mutation signal detection and inhibition component, a small-amplitude mutation signal detection component, a notch component and a buffer moment determination component, wherein,
a cache component: caching the current sampling time tiA plurality of buffer instants t in a previous time period0、t1、...、ti-1Trapped wave output electrocardiosignal d [0 ]]、d[1]、...、d[i-1]Wherein i is a natural number greater than or equal to 2, and the time period has a length of [10ms,30 ms%]Value in the range, the caching time t0、t1、...、ti-1Time t is cached according to time sequencei-1Closest to the current sampling instant ti；
Giant mutation signal detection and suppression means: for the current sampling time tiSampled original electrocardiosignal d0[i]Detecting and inhibiting the great amplitude mutation signal to obtain the current sampling time tiCardiac electric signal d [ i ]]；
Small-amplitude abrupt-change-signal detection section: is calculated at time t1、...、ti-1、tiIs the absolute value of the slope | k [ n ] of each electrocardiographic signal]|：
|k[n]|＝|(d[n]-d[n-1])/(tn-tn-1)|，
Where n is 1, if | k [1 ]]|、|k[2]|、...、|k[i-1]The average value of | is less than the threshold value L of the rate of change of the electrocardiosignal per unit time, and | k [ i |)]If | is greater than the threshold value H of the change rate of the electrocardiosignals in unit time, the current sampling time t is judgediCardiac electric signal d [ i ]]Presence of small mutations;
a trap member: if the current sampling time tiCardiac electric signal d [ i ]]If small sudden change exists, a first filter is adopted for carrying out trapped wave output;
buffering time determination means: if the current sampling time tiCardiac electric signal d [ i ]]If there is no small sudden change, determining the current sampling time tiBelonging to the caching time.
The method for inhibiting the ringing of the notch filter in the process of acquiring the electrocardiosignal has the advantages of high calculation efficiency, simplicity and convenience in implementation and strong applicability.
Drawings
FIG. 1 is a schematic waveform of an electrocardiographic signal;
FIG. 2 is a waveform of an original cardiac signal prior to notching;
FIG. 3 is a waveform of an electrocardiosignal on which ringing occurs without using the method of suppressing ringing of a notch filter according to the embodiment of the present invention;
FIG. 4 is a flow diagram of a method of suppressing notch filter ringing during cardiac signal acquisition in accordance with one embodiment of the present invention;
FIG. 5 is a waveform of an ECG signal obtained by suppressing ringing of a notch filter according to an embodiment of the present invention;
fig. 6 is a flow chart of a method of suppressing notch filter ringing during cardiac signal acquisition in accordance with yet another embodiment of the present invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the present invention more apparent, the present invention is described in further detail below with reference to specific embodiments and the accompanying drawings. Those skilled in the art will appreciate that the present invention is not limited to the drawings and the following examples.
The embodiment of the invention provides a method for inhibiting ringing of a notch filter in an electrocardiosignal acquisition process, which is characterized in that an acquired electrocardiosignal is processed before notch, for example, as shown in figure 2, the horizontal axis represents time in milliseconds ms, and the vertical axis represents the electrocardiosignal intensity in microvolt muV. It should be understood by those skilled in the art that fig. 2 is only a schematic diagram, the human electrocardiosignal is acquired in real time, and the method of the embodiment of the invention is applied to carry out notching in real time, so as to suppress the ringing of the notch filter.
As shown in fig. 4, the method for suppressing ringing of a notch filter in an electrocardiographic signal acquisition process according to an embodiment of the present invention samples an electrocardiographic signal in real time to acquire the electrocardiographic signal, and includes the following steps:
a caching step: caching the current sampling time tiA plurality of buffer instants t in a previous time period0、t1、...、ti-1Trapped wave output electrocardiosignal d [0 ]]、d[1]、...、d[i-1]Wherein i is a natural number greater than or equal to 2, and the time period has a length of [10ms,30 ms%]Value in the range, the caching time t0、t1、...、ti-1Time t is cached according to time sequencei-1Closest to the current sampling instant ti。
Detecting and inhibiting a large amplitude mutation signal: obtaining the current sampling time tiOf the original cardiac signal d0[i]Previous buffering time ti-1The electrocardiosignal d [ i-1 ]]The sampling time interval of two electrocardiosignals is ti-ti-1Calculating the gradient k [ i ] of the electrocardiosignal at the current sampling moment]Comprises the following steps:
k[i]＝(d0[i]-d[i-1])/(ti-ti-1)，
if the slope k [ i ] of the electrocardiosignal at the current sampling moment]Absolute value of | k [ i]If | is greater than the preset electrocardiosignal change threshold value A in unit time, determining the electrocardiosignal at the current sampling moment as a large-amplitude mutation signal, and determining the current sampling moment tiCardiac electric signal d [ i ]]Comprises the following steps:
d[i]＝d[i-1]+(k[i]/|k[i]|)*A，
thereby forcibly inhibiting the large-amplitude mutation signal and entering the small-amplitude mutation signal detection step. If the current sampling time tiGradient k [ i ] of electrocardiosignal]Is less than the set electrocardiosignal change threshold value A in unit time, the current sampling moment t is determinediThe electrocardiosignal of (2) has no great amplitude mutation, d [ i ]]＝d0[i]And entering a small-amplitude mutation signal detection step.
The set electrocardiosignal change threshold value A per unit time is preferably set to be 1000 muV per ms, and can also be a value within the range of [800 muV, 1200 muV ]. The unit of the set electrocardiosignal change threshold value A per unit time is related to the electrocardiosignal and the time unit.
It will be understood by those skilled in the art that the detection of the large amplitude mutation signal is relatively easy, and there are various methods for correcting/suppressing the large amplitude mutation signal, which are not limited to the above-mentioned methods provided in the embodiments of the present invention, and for example, the detection of the large amplitude mutation signal may be performed by comparing the change rates of the two previous and subsequent sampling signals, so as to determine whether to suppress the large amplitude mutation signal.
Detecting a small-amplitude mutation signal: is calculated at time t1、t2、...、ti-2、ti-1、tiIs the absolute value of the slope | k [ n ] of each electrocardiographic signal]I (i.e., | k [1 ]]|、|k[2]|、...、|k[i-1]|、|k[i]I) is:
|k[n]|＝|(d[n]-d[n-1])/(tn-tn-1)|，
where n is 1, if | k [1 ]]|、|k[2]|、...、|k[i-1]The average value of | is less than the threshold value L of the change rate of the electrocardiosignals in unit time, which is 20uV/ms, and | k [ i |]If the change rate threshold value H of the electrocardiosignal, | is greater than the unit time is 80uV/ms, the current sampling time t is judgediCardiac electric signal d [ i ]]There was a small mutation.
The above-mentioned electrocardiographic signal change rate threshold L per unit time is 20uV/ms, and the electrocardiographic signal change rate threshold H per unit time is 80uV/ms, which are preferable examples of the embodiment of the present invention, the electrocardiographic signal change rate threshold L per unit time may be set in a range of [10 μ V/ms,30 μ V/ms ], and the electrocardiographic signal change rate threshold H per unit time may be set in a range of [60 μ V/ms,100 μ V/ms ].
A trapping step: if the current sampling time tiCardiac electric signal d [ i ]]And if the small abrupt change exists, the first filter is adopted for notch output. If the current sampling time tiCardiac electric signal d [ i ]]And if the small abrupt change does not exist, performing notch output by adopting a second filter.
A cache time determining step: if the current sampling time tiCardiac electric signal d [ i ]]If there is a small sudden change, determining the current sampling time tiNot belonging to the caching moment; if the current sampling time tiCardiac electric signal d [ i ]]If there is no small sudden change, determining the current sampling time tiBelonging to the caching moment;
and returning to the step: and returning to the caching step, and processing the electrocardiosignals sampled subsequently.
I.e. if the current sampling instant tiCardiac electric signal d [ i ]]Determining sampling time t when there is small abrupt changeiNot belonging to the buffer time, the next sampling time ti+1In the process of processing the electrocardiosignals, the sampling time t is not determined in the step of buffering the electrocardiosignalsiAnd caching the electrocardiosignals output by the trapped wave. With the continuous operation of the method of the embodiment of the invention, the buffered electrocardiosignals are all electrocardiosignals without small mutation.
The reason why the first filter is adopted to trap the electrocardiosignals with small amplitude mutation and the second filter is adopted to trap the electrocardiosignals without small amplitude mutation in the embodiment is that generally, the filters have buffer memory or feedback, the previous output of the filters can influence the current output of the filters, and the two independent filters are adopted to respectively process the small amplitude mutation electrocardiosignals and the normal electrocardiosignals, so that the influence of the small amplitude mutation electrocardiosignals on the trap of the normal electrocardiosignals can be avoided, and a better output effect can be obtained. Of course, the first filter may also be used for notching normal cardiac signals if the first filter itself is not buffered or the above effects are negligible. The filter used in this embodiment may be an FIR filter or an IIR filter.
It should be noted that, when the acquisition of the electrocardiographic signals is started, the buffered electrocardiographic signals are less, and the effect of suppressing ringing of the notch filter is limited, but as the method of the embodiment of the present invention continues, the data buffer is updated, and a better output image can be obtained. By adopting the method for inhibiting the ringing of the notch filter in the electrocardiosignal acquisition process, the acquired electrocardiosignals can be processed, the ringing of the notch filter can be effectively inhibited, and the electrocardiosignal image shown in figure 5 is obtained, wherein the horizontal axis represents time in milliseconds ms, and the vertical axis represents the electrocardiosignal intensity in microvolt muV.
In another embodiment of the present invention, a method for suppressing ringing of a notch filter in an electrocardiographic signal obtaining process is provided, which samples an electrocardiographic signal in real time to obtain the electrocardiographic signal, and includes the following steps:
a caching step: the time interval of electrocardiosignal sampling is equal time interval of 2ms, and the current sampling time t is cachediA plurality of buffer instants t within a preceding time period of 16ms0、t1、t2、...、t7Trapped wave output electrocardiosignal d [0 ]]、d[1]、...、d[7]。
Detecting and inhibiting a large amplitude mutation signal: for the current sampling time t8Of the original cardiac signal d0[8]Detecting and inhibiting the great amplitude mutation signal to obtain the current sampling time t8Cardiac electric signal d [8 ]]And entering a small-amplitude mutation signal detection step.
Detecting a small-amplitude mutation signal: is calculated at time t1、t2、...、t7、t8Is the absolute value of the slope | k [ n ] of each electrocardiographic signal]I (i.e., | k [1 ]]|、|k[2]|、...、|k[7]|、|k[8]I) is:
|k[n]|＝|(d[n]-d[n-1])/(tn-tn-1)|，
where n is 1, 2.., 8, if | k [1 ]]|、|k[2]|、...、|k[7]The average value of | is less than the threshold value L of the change rate of the electrocardiosignals in unit time, 20uV/ms, and | k [8 ]]If the threshold value H of the change rate of the electrocardiosignals, | is larger than the unit time is 80uV/ms, the judgment is madeCurrent sampling instant t8Cardiac electric signal d [ i ]]There was a small mutation.
A trapping step: due to the current sampling time t8Cardiac electric signal d [8 ]]There is a small abrupt change, so the first filter is adopted for the notch output.
A cache time determining step: current sampling instant t8Cardiac electric signal d [8 ]]There is a small abrupt change, thus determining the current sampling instant t8Not belonging to the buffering time.
And returning to the step: returning to the caching step, and carrying out subsequent sampling time t9Cardiac electric signal d [9 ]]And (4) processing. At the next moment t9Cardiac electric signal d [9 ]]During the processing, in the buffering step, the sampling time t8Not belonging to the buffering time, the buffered electrocardiosignals are seven buffering times t1、t2、...、t6、t7And a trapped wave output electrocardiosignal d [1 ]]、d[2]、...、d[6]、d[7]。
As shown in fig. 6, in a further embodiment of the present invention, a method for suppressing ringing of a notch filter in an electrocardiographic signal acquisition process is provided, which samples an electrocardiographic signal in real time to acquire the electrocardiographic signal, and includes the following steps:
a caching step: caching the current sampling time tiA plurality of buffer instants t in a previous time period0、t1、...、ti-1Trapped wave output electrocardiosignal d [0 ]]、d[1]、...、d[i-1]Wherein i is a natural number greater than or equal to 2, and the time period has a length of [10ms,30 ms%]Values within the range.
A time interval judging step: obtaining the current sampling time tiAnd the previous buffering time ti-1Time interval t betweeni-ti-1If the time interval t isi-ti-1If the set time threshold is exceeded for 500ms, the current sampling time t is sampled by using a second filteriCardiac electric signal d [ i ]]Carrying out notch output and determining the current sampling time tiReturning to the caching step at the caching time, and performing the next time ti+1Processing the electrocardiosignals; if the time interval ti-ti-1And if the time does not exceed 500ms, entering a step of detecting and inhibiting the large-amplitude mutation signal.
Detecting and inhibiting a large amplitude mutation signal: for the current sampling time tiSampled original electrocardiosignal d0[i]Detecting and inhibiting the great amplitude mutation signal to obtain the current sampling time tiCardiac electric signal d [ i ]]And then entering a small-amplitude mutation signal detection step.
Detecting a small-amplitude mutation signal: is calculated at time t1、t2、...、ti-2、ti-1、tiIs the absolute value of the slope | k [ n ] of each electrocardiographic signal]I (i.e., | k [1 ]]|、|k[2]|、...、|k[i-1]|、|k[i]I) is:
|k[n]|＝|(d[n]-d[n-1])/(tn-tn-1)|，
where n is 1, if | k [1 ]]|、|k[2]|、...、|k[i-1]The average value of | is less than the threshold value L of the change rate of the electrocardiosignals in unit time, which is 20uV/ms, and | k [ i |]If the change rate threshold value H of the electrocardiosignal, | is greater than the unit time is 80uV/ms, the current sampling time t is judgediCardiac electric signal d [ i ]]There was a small mutation.
A trapping step: if the current sampling time tiCardiac electric signal d [ i ]]And if the small abrupt change exists, the first filter is adopted for notch output. If the current electrocardiosignal d [ i ]]And if the small abrupt change does not exist, performing notch output by adopting a second filter.
A cache time determining step: if the current sampling time tiCardiac electric signal d [ i ]]If there is a small sudden change, determining the current sampling time tiNot belonging to the caching moment; if the current sampling time tiCardiac electric signal d [ i ]]If there is no small sudden change, determining the current sampling time tiBelonging to the caching moment;
and returning to the step: and returning to the caching step, and processing the electrocardiosignals sampled subsequently.
The embodiment of the invention also provides a system for inhibiting the ringing of the notch filter in the electrocardiosignal acquisition process, which comprises a buffer component, a large-amplitude mutation signal detection and inhibition component, a small-amplitude mutation signal detection component, a notch component and a buffer moment determination component, wherein,
a cache component: caching the current sampling time tiA plurality of buffer instants t in a previous time period0、t1、...、ti-1Trapped wave output electrocardiosignal d [0 ]]、d[1]、...、d[i-1]Wherein i is a natural number greater than or equal to 2, and the time period has a length of [10ms,30 ms%]Value in the range, the caching time t0、t1、...、ti-1Time t is cached according to time sequencei-1Closest to the current sampling instant ti；
Giant mutation signal detection and suppression means: for the current sampling time tiSampled original electrocardiosignal d0[i]Detecting and inhibiting the great amplitude mutation signal to obtain the current sampling time tiCardiac electric signal d [ i ]]Entering a small-amplitude mutation signal detection step;
small-amplitude abrupt-change-signal detection section: is calculated at time t1、...、ti-1、tiIs the absolute value of the slope | k [ n ] of each electrocardiographic signal]|：
|k[n]|＝|(d[n]-d[n-1])/(tn-tn-1)|，
Where n is 1, if | k [1 ]]|、|k[2]|、...、|k[i-1]The average value of | is less than the threshold value L of the rate of change of the electrocardiosignal per unit time, and | k [ i |)]If | is greater than the threshold value H of the change rate of the electrocardiosignals in unit time, the current sampling time t is judgediCardiac electric signal d [ i ]]Presence of small mutations;
a trap member: if the current sampling time tiCardiac electric signal d [ i ]]If small sudden change exists, a first filter is adopted for carrying out trapped wave output;
buffering time determination means: if the current sampling time tiCardiac electric signal d [ i ]]If there is no small sudden change, determining the current sampling time tiBelonging to the caching time.
Embodiments of the present invention further provide a computer-readable storage medium, on which a computer program is stored, where the computer program, when executed by a processor, implements the steps of the above method.
A computer device comprising a memory, a processor and a computer program stored on the memory and executable on the processor, the processor implementing the steps of the method when executing the program.
Those of skill in the art will understand that the logic and/or steps represented in the flowcharts or otherwise described herein, e.g., an ordered listing of executable instructions that can be viewed as implementing logical functions, can be embodied in any computer-readable medium for use by or in connection with an instruction execution system, apparatus, or device, such as a computer-based system, processor-containing system, or other system that can fetch the instructions from the instruction execution system, apparatus, or device and execute the instructions. For the purposes of this description, a "computer-readable medium" can be any means that can contain, store, communicate, propagate, or transport the program for use by or in connection with the instruction execution system, apparatus, or device.
More specific examples (a non-exhaustive list) of the computer-readable medium would include the following: an electrical connection (electronic device) having one or more wires, a portable computer diskette (magnetic device), a Random Access Memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or flash memory), an optical fiber device, and a portable compact disc read-only memory (CDROM). Additionally, the computer-readable medium could even be paper or another suitable medium upon which the program is printed, as the program can be electronically captured, via for instance optical scanning of the paper or other medium, then compiled, interpreted or otherwise processed in a suitable manner if necessary, and then stored in a computer memory.
It should be understood that portions of the present invention may be implemented in hardware, software, firmware, or a combination thereof. In the above embodiments, the various steps or methods may be implemented in software or firmware stored in memory and executed by a suitable instruction execution system. For example, if implemented in hardware, as in another embodiment, any one or combination of the following techniques, which are known in the art, may be used: a discrete logic circuit having a logic gate circuit for implementing a logic function on a data signal, an application specific integrated circuit having an appropriate combinational logic gate circuit, a Programmable Gate Array (PGA), a Field Programmable Gate Array (FPGA), or the like.
In the description herein, references to the description of the term "one embodiment," "some embodiments," "an example," "a specific example," or "some examples," etc., mean 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, the schematic representations of the terms used above do not necessarily refer 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.
The embodiments of the present invention have been described above. However, the present invention is not limited to the above embodiment. Any modification, equivalent replacement, or improvement made within the spirit and principle of the present invention should be included in the protection scope of the present invention.
Claims (10)
1. A method for inhibiting the ringing of a notch filter in the electrocardiosignal application process is characterized in that: the method comprises the following steps:
a caching step: caching the current sampling time tiA plurality of buffer instants t in a previous time period0、t1、...、ti-1Trapped wave output electrocardiosignal d [0 ]]、d[1]、...、d[i-1]Wherein i is a natural number greater than or equal to 2, and the time period has a length of [10ms,30 ms%]Value in the range, the caching time t0、t1、...、ti-1Time t is cached according to time sequencei-1Closest to the current sampling instant ti；
Detecting and inhibiting a large amplitude mutation signal: for the current sampling time tiSampled original electrocardiosignal d0[i]Detecting and inhibiting the great amplitude mutation signal to obtain the current sampling momenttiCardiac electric signal d [ i ]]Entering a small-amplitude mutation signal detection step;
detecting a small-amplitude mutation signal: is calculated at time t1、...、ti-1、tiIs the absolute value of the slope | k [ n ] of each electrocardiographic signal]|：
|k[n]|＝|(d[n]-d[n-1])/(tn-tn-1)|，
Where n is 1, if | k [1 ]]|、|k[2]|、...、|k[i-1]The average value of | is less than the threshold value L of the rate of change of the electrocardiosignal per unit time, and | k [ i |)]If | is greater than the threshold value H of the change rate of the electrocardiosignals in unit time, the current sampling time t is judgediCardiac electric signal d [ i ]]Presence of small mutations;
a trapping step: if the current sampling time tiCardiac electric signal d [ i ]]If small sudden change exists, a first filter is adopted for carrying out trapped wave output;
a cache time determining step: if the current sampling time tiCardiac electric signal d [ i ]]If there is no small sudden change, determining the current sampling time tiBelonging to the caching moment;
and returning to the step: and returning to the caching step.
2. The method of claim 1, wherein: in the step of detecting and inhibiting the great amplitude mutation signal, the current sampling time t is obtainediOf the original cardiac signal d0[i]Previous buffering time ti-1The electrocardiosignal d [ i-1 ]]Calculating the gradient k [ i ] of the electrocardiosignal at the current sampling moment]Comprises the following steps:
k[i]＝(d0[i]-d[i-1])/(ti-ti-1)，
if the slope k [ i ] of the electrocardiosignal at the current sampling moment]Absolute value of | k [ i]If | is greater than the preset electrocardiosignal change threshold value A in unit time, determining the electrocardiosignal at the current sampling moment as a large-amplitude mutation signal, and determining the current sampling moment tiCardiac electric signal d [ i ]]Comprises the following steps:
d[i]＝d[i-1]+(k[i]/|k[i]|)*A；
if the current sampling time tiGradient k [ i ] of electrocardiosignal]Is less than a set unit timeChange threshold A of electrocardiosignal, current sampling time tiCardiac electric signal d [ i ]]Comprises the following steps: d [ i ]]＝d0[i]。
3. The method of claim 2, wherein: in the step of detecting and inhibiting the great mutation signal, the set electrocardiosignal change threshold A of each ms takes values in the range of [800 muV, 1200 muV ].
4. The method of claim 1, wherein: if the current sampling time tiCardiac electric signal d [ i ]]And if the small-amplitude abrupt change does not exist, performing notching output by adopting a first filter in the notching step, wherein the first filter is a filter without a buffer function.
5. The method of claim 1, wherein: if the current sampling time tiCardiac electric signal d [ i ]]And if the small-amplitude abrupt change does not exist, performing notching output on the small-amplitude abrupt change by adopting a second filter in the notching step.
6. The method of claim 5, wherein: after the buffering step, the method further comprises a time interval judging step of acquiring the current sampling time tiAnd the previous buffering time ti-1Time interval t betweeni-ti-1If the time interval t isi-ti-1If the set time threshold is exceeded, the second filter is used for the current sampling time tiOf the original cardiac signal d0[i]Carrying out notch output and determining the current sampling time tiReturning to the caching step at the caching moment to process the electrocardiosignals at the next moment; if the time interval ti-ti-1And if the set time threshold is not exceeded, entering a step of detecting and inhibiting the large-amplitude mutation signal.
7. The method of claim 1, wherein: in the buffering step, the buffering time period is 16 ms.
8. The method of claim 7, wherein: the time interval of the electrocardiosignal sampling is equal time interval 2 ms.
9. The method of any of claims 1-8, wherein: the electrocardiosignal change rate threshold value L in unit time is taken as a value in the range of [10 muV/ms, 30 muV/ms ], and the electrocardiosignal change rate threshold value H in unit time is taken as a value in the range of [60 muV/ms, 100 muV/ms ].
10. A system for restraining the ringing of a notch filter in the electrocardiosignal acquisition process is characterized in that: the system comprises a buffer unit, a large amplitude sudden change signal detection and suppression unit, a small amplitude sudden change signal detection unit, a trap unit and a buffer time determination unit, wherein,
a cache component: caching the current sampling time tiA plurality of buffer instants t in a previous time period0、t1、...、ti-1Trapped wave output electrocardiosignal d [0 ]]、d[1]、...、d[i-1]Wherein i is a natural number greater than or equal to 2, and the time period has a length of [10ms,30 ms%]Value in the range, the caching time t0、t1、...、ti-1Time t is cached according to time sequencei-1Closest to the current sampling instant ti；
Giant mutation signal detection and suppression means: for the current sampling time tiSampled original electrocardiosignal d0[i]Detecting and inhibiting the great amplitude mutation signal to obtain the current sampling time tiCardiac electric signal d [ i ]]；
Small-amplitude abrupt-change-signal detection section: is calculated at time t1、...、ti-1、tiIs the absolute value of the slope | k [ n ] of each electrocardiographic signal]|：
|k[n]|＝|(d[n]-d[n-1])/(tn-tn-1)|，
Where n is 1, if | k [1 ]]|、|k[2]|、...、|k[i-1]The average value of | is less than the threshold value L of the rate of change of the electrocardiosignal per unit time, and | k [ i |)]Electrocardiosignal with | larger than unit timeThe threshold value H of the change rate judges the current sampling time tiCardiac electric signal d [ i ]]Presence of small mutations;
a trap member: if the current sampling time tiCardiac electric signal d [ i ]]If small sudden change exists, a first filter is adopted for carrying out trapped wave output;
buffering time determination means: if the current sampling time tiCardiac electric signal d [ i ]]If there is no small sudden change, determining the current sampling time tiBelonging to the caching time.
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