Blood pressure monitoring system and signal processing method

Abstract

The present disclosure describes a blood pressure monitoring system and a signal processing method, which is used to obtain a blood pressure signal sampling waveform of the change of intravascular pressure with time, including a plurality of cardiac cycles; in the blood pressure signal sampling waveform, a continuous cycle signal waveform including a predetermined number of cardiac cycles is selected, if the fluctuation of the peak value of the continuous cycle signal waveform is not greater than a first threshold value and the fluctuation of the valley value of the continuous cycle signal waveform is not greater than a second threshold value, the effective peak value and the effective valley value of the continuous cycle signal waveform are calculated; the reference peak value and the reference valley value are obtained based on the effective peak value and the effective valley value; the normal pressure value in the blood pressure signal sampling waveform is identified and marked based on the reference peak value and the reference valley value; and the effective value of the intravascular pressure corresponding to the single cycle signal waveform is obtained based on the single cycle signal waveform including one cardiac cycle and the pressure value marked as normal. According to the present disclosure, the adverse effects of signal abnormalities caused by wall attachment can be effectively reduced.

Description

[0001] This application is a divisional application of the patent application with application number 2020116420319, titled "Intravascular pressure measurement system", and filed on December 31, 2020. TECHNICAL FIELD

[0002] The present disclosure relates to a blood pressure monitoring system and a signal processing method. BACKGROUND

[0003] For many cardiovascular diseases such as coronary heart disease, the stenosis of blood vessels (e.g., caused by blood vessel plaques) affects blood supply, which brings great harm to patients. At present, percutaneous coronary intervention (PCI) is a relatively effective treatment for such diseases. In the traditional method, doctors usually visually estimate the stenosis degree of the stenosis lesion by coronary angiography to determine whether to perform intervention treatment. However, this traditional method is difficult to help doctors accurately assess the degree of influence of the stenosis lesion on blood supply, which may lead to improper treatment.

[0004] In recent years, in order to more accurately determine whether a patient truly needs to perform intervention treatment, the degree of influence of the stenosis lesion on blood supply is increasingly applied and promoted based on the Fractional Flow Reverse (FFR). FFR is defined as the ratio of the maximum blood flow that the myocardial region supplied by the coronary artery with the stenosis lesion can obtain to the maximum blood flow that the same region can obtain under normal circumstances. In order to calculate the FFR of a given stenosis in the coronary artery, the average pressure (Pd) on the distal side of the stenosis (e.g., downstream of the stenosis, away from the aorta) and the average pressure (Pa) on the proximal side of the stenosis (e.g., upstream of the stenosis, close to the aorta) need to be measured respectively.

[0005] At present, a pressure measuring instrument is usually used to measure the pressure in the blood vessel at a predetermined position in the blood vessel, such as measuring the average pressure (Pd) on the distal side of the stenosis, so as to measure the FFR. However, in the above pressure measurement process, the phenomenon of the pressure measuring instrument adhering to the wall may occur, which may cause abnormality of the measured blood pressure signal. SUMMARY

[0006] The present disclosure is proposed in view of the above-mentioned prior art, and aims to provide a signal processing method for intravascular pressure measurement, which can effectively reduce the adverse effects of signal abnormality caused by adhesion.

[0007] To this end, the present disclosure provides a signal processing method for intravascular pressure measurement, which is characterized in that, a pressure measurement is performed at a predetermined position in a blood vessel by a pressure measurement instrument at a predetermined sampling frequency to obtain a blood pressure signal sampling waveform of the intravascular pressure varying with time, the blood pressure signal sampling waveform comprises a plurality of cardiac cycles, a continuous cycle signal waveform comprising a predetermined number of cardiac cycles is selected from the blood pressure signal sampling waveform, it is determined whether the fluctuation of the peak value of the continuous cycle signal waveform is not greater than a first threshold value, and it is determined whether the fluctuation of the valley value of the continuous cycle signal waveform is not greater than a second threshold value, if the fluctuation of the peak value of the continuous cycle signal waveform is not greater than the first threshold value and the fluctuation of the valley value of the continuous cycle signal waveform is not greater than the second threshold value, the effective peak value and the effective valley value of the continuous cycle signal waveform are calculated, the reference peak value and the reference valley value are obtained based on the effective peak value and the effective valley value, it is determined whether each pressure value in the blood pressure signal sampling waveform falls within the range of the reference peak value and the reference valley value, if the pressure value falls within the range, the pressure value is marked as normal, a single cycle signal waveform comprising one cardiac cycle is selected from the blood pressure signal sampling waveform, and if the ratio of the number of pressure values marked as normal to the number of all pressure values in the single cycle signal waveform is not less than a third threshold value, the effective value of the intravascular pressure corresponding to the single cycle signal waveform is calculated based on the pressure values marked as normal in the single cycle signal waveform.

[0008] In the signal processing method involved in the present disclosure, the blood pressure signal sampling waveform of the intravascular pressure varying with time is obtained in the blood vessel by a pressure measurement instrument, the reference peak value and the reference valley value are obtained based on the continuous cycle signal waveform comprising a predetermined number of cardiac cycles, and the pressure values normal in the blood pressure signal sampling waveform are marked based on the reference peak value and the reference valley value, and then the effective value of the intravascular pressure corresponding to the single cycle signal waveform is calculated based on the pressure values normal in the single cycle signal waveform comprising one cardiac cycle. In this case, the effective value of the intravascular pressure corresponding to one cardiac cycle is calculated based on the pressure values normal in the cardiac cycle, thereby effectively reducing the adverse effects of signal abnormalities caused by adhesion.

[0009] In addition, in the signal processing method involved in the present disclosure, optionally, it further comprises determining whether the ratio of the interval of adjacent peak values of the continuous cycle signal waveform to the cardiac cycle falls within a first interval, and determining whether the ratio of the interval of adjacent valley values of the continuous cycle signal waveform to the cardiac cycle falls within a second interval, if the ratio of the interval of adjacent peak values of the continuous cycle signal waveform to the cardiac cycle falls within the first interval and the ratio of the interval of adjacent valley values of the continuous cycle signal waveform to the cardiac cycle falls within the second interval, the effective peak value and the effective valley value of the continuous cycle signal waveform are calculated. In this way, the effective peak value and the effective valley value can be more accurately obtained.

[0010] In addition, in the signal processing method, optionally, if the fluctuation of the peak value of the continuous periodic signal waveform is greater than the first threshold value or the fluctuation of the valley value of the continuous periodic signal waveform is greater than the second threshold value, the continuous periodic signal waveform is re-selected. In this case, by judging the fluctuation of the peak value and the fluctuation of the valley value, a continuous periodic signal waveform more suitable for calculating the effective peak value and the effective valley value can be selected.

[0011] In addition, in the signal processing method, optionally, if the fluctuation of the peak value of the continuous periodic signal waveform is not greater than the first threshold value and the fluctuation of the valley value of the continuous periodic signal waveform is not greater than the second threshold value, the effective peak value is the average of the peak values of the continuous periodic signal waveform, and the effective valley value is the average of the valley values of the continuous periodic signal waveform. Thus, by averaging calculation, the effective peak value and the effective valley value can be easily obtained.

[0012] In addition, in the signal processing method, optionally, the reference peak value is obtained based on the effective peak value and the difference between the effective peak value and the effective valley value, and the reference valley value is obtained based on the effective valley value and the difference between the effective peak value and the effective valley value. Thus, the reference range can be effectively set.

[0013] In addition, in the signal processing method, optionally, in the single-period signal waveform, if the ratio of the number of pressure values marked as normal to the number of all pressure values is not less than the third threshold value, the average of all pressure values marked as normal in the single-period signal waveform is used as the effective value of the intravascular pressure corresponding to the single-period signal waveform. Thus, the effective value of the intravascular pressure can be more accurately obtained.

[0014] In addition, in the signal processing method, optionally, in the single-period signal waveform, if the ratio of the number of pressure values marked as normal to the number of all pressure values is not less than the third threshold value, the cardiac cycle corresponding to the single-period signal waveform is marked as effective, and if the ratio of the number of pressure values marked as normal to the number of all pressure values is less than the third threshold value, the cardiac cycle corresponding to the single-period signal waveform is marked as ineffective.

[0015] In addition, in the signal processing method, optionally, in the single-period signal waveform, if the ratio of the number of pressure values marked as normal to the number of all pressure values is less than the third threshold value, the effective value of the intravascular pressure corresponding to the single-period signal waveform is obtained based on at least one cardiac cycle marked as effective closest to the single-period signal waveform.

[0016] In addition, in the signal processing method according to the present disclosure, the pressure measuring instrument can include a pressure sensor for acquiring a blood pressure signal and a pushing tool for pushing the pressure sensor.

[0017] Furthermore, the present disclosure also provides an intravascular pressure measuring system using the signal processing method according to the present disclosure.

[0018] According to the present disclosure, the adverse effects of signal abnormalities caused by wall attachment during intravascular pressure measurement can be effectively reduced. BRIEF DESCRIPTION OF DRAWINGS

[0019] The present disclosure will now be explained in further detail by way of example only with reference to the accompanying drawings, in which:

[0020] Figure 1 is a schematic diagram showing the application of the FFR measuring system according to the example of the present disclosure.

[0021] Figure 2 is an enlarged schematic diagram showing the intervention of the proximal pressure measuring instrument and the distal pressure measuring instrument into the blood vessel according to the example of the present disclosure.

[0022] Figure 3 is a block diagram schematic of the signal processor according to the example of the present disclosure.

[0023] Figure 4 is a schematic diagram showing the blood pressure signal sampling waveform according to the example of the present disclosure.

[0024] Figure 5 is a schematic diagram showing the continuous periodic signal waveform according to the example of the present disclosure.

[0025] Figure 6A is a schematic diagram showing the display of the unprocessed FFR by the display device according to the example of the present disclosure.

[0026] Figure 6B is a schematic diagram showing the display of the effective value of the FFR by the display device according to the example of the present disclosure.

[0027] Figure 7A is a schematic diagram showing the overall flow of the signal processing method for FFR measurement according to the example of the present disclosure.

[0028] Figure 7B is a schematic diagram showing the flow of acquiring the reference peak value and the reference valley value according to the example of the present disclosure.

[0029] Figure 8 is a schematic diagram showing the flow of the signal processing method for intravascular pressure measurement according to the example of the present disclosure. DETAILED DESCRIPTION

[0030] Hereinafter, preferred embodiments of the present disclosure will be described in detail with reference to the accompanying drawings. In the following description, for the sake of explanation, identical configurations are designated by identical reference numerals, and repetitive explanations are omitted. In addition, the drawings are schematic views, and the ratio of the dimensions between the components or the shape of the components, etc. can be different from the actual ones.

[0031] It should be noted that the terms "comprising" and "having" and any variations thereof, such as a process, a method, a system, a product, or an apparatus including or having a series of steps or units, are not necessarily limited to those steps or units clearly listed, but can include or have other steps or units that are not clearly listed or inherent to the process, the method, the product, or the apparatus.

[0032] In addition, the subheadings and the like involved in the following description of the present disclosure are not intended to limit the content or the scope of the present disclosure, but merely serve as a reading aid. Such subheadings should not be understood as dividing the content of the article, nor should the content under the subheadings be limited only within the scope of the subheadings.

[0033] Embodiments of the present disclosure provide an intravascular pressure measurement system that can acquire and process a blood pressure signal at a predetermined position in a blood vessel to obtain an effective value of an intravascular pressure at the predetermined position. In various embodiments, the intravascular pressure measurement system can also be referred to as a pressure measurement system, a blood pressure measurement system, a blood pressure monitoring system, etc.

[0034] Embodiments of the present disclosure provide an FFR measurement system that can acquire and process a blood pressure signal at a predetermined position in a blood vessel to obtain an effective value of an FFR at the predetermined position. In various embodiments, the FFR measurement system can also be referred to as a medical measurement system, an FFR monitoring system, etc. Embodiments of the present disclosure provide an intravascular pressure measurement signal processing method that can process an acquired blood pressure signal at a predetermined position in a blood vessel to obtain an effective value of an intravascular pressure.

[0035] Embodiments of the present disclosure provide an FFR measurement signal processing method that can process an acquired blood pressure signal at a predetermined position in a blood vessel to obtain an effective value of an FFR.

[0036] Figure 1 FIG. 1 is a schematic view showing an application of an FFR measurement system 1 according to an example of the present disclosure.

[0037] Figure 2 FIG. 2 is an enlarged schematic view showing an intravascular intervention of a proximal pressure measurement instrument 10 and a distal pressure measurement instrument 20 according to an example of the present disclosure.

[0038] In various embodiments, the FFR measurement system 1 can acquire blood pressure signals at predetermined positions within a blood vessel, and process the acquired blood pressure signals to obtain an effective value of FFR. In various embodiments, if there is a stenosis S in a blood vessel (e.g., a coronary artery), the FFR measurement system 1 can acquire blood pressure signals at both sides of the stenosis S in the blood vessel, i.e., a proximal side S p and a distal side S d of the stenosis S, and process the acquired blood pressure signals at both sides of the stenosis S to obtain an effective value of FFR.

[0039] In various embodiments, the FFR measurement system 1 can include a proximal pressure measurement instrument 10, a distal pressure measurement instrument 20, and a signal processor 30 (see Figure 1 and Figure 2 ). The proximal pressure measurement instrument 10 can acquire blood pressure signals at the proximal side S p of the stenosis S, the distal pressure measurement instrument 20 can acquire blood pressure signals at the distal side S d of the stenosis S, and the signal processor 30 can receive and process the blood pressure signals at the proximal side S p of the stenosis S and the blood pressure signals at the distal side S d of the stenosis S to obtain an effective value of FFR.

[0040] In various embodiments, the FFR measurement system 1 can further include a display device 40 (see Figure 1 ). The display device 40 can display the blood pressure signals at the proximal side S p of the stenosis S, the blood pressure signals at the distal side S d of the stenosis S, or the effective value of FFR.

[0041] In various embodiments, the proximal pressure measurement instrument 10 can be connected to an outlet of a coronary artery to measure blood pressure signals at the outlet of the coronary artery. In various embodiments, the proximal pressure measurement instrument 10 can be connected to the proximal side S p of the stenosis S to acquire blood pressure signals at the proximal side S p of the stenosis S (see Figure 2 ). For example, the proximal pressure measurement instrument 10 can be connected to the proximal side S p of the stenosis S via an interventional blood vessel and a hollow guide catheter extending from the proximal side S p of the stenosis S to outside of the body.

[0042] In various embodiments, the blood pressure signals at the proximal side S p of the stenosis S acquired by the proximal pressure measurement instrument 10 can be analog signals. In various embodiments, the blood pressure signals at the proximal side S pThe blood pressure signal of the stenosis proximal side S p The blood pressure signal of the stenosis proximal side S p The average pressure of the stenosis proximal side S p The blood pressure signal of the stenosis proximal side S p is converted into a digital signal that can be used to represent the pressure value, and is averaged.

[0043] The blood pressure signal of the stenosis proximal side S p The blood pressure signal of the stenosis proximal side S p The blood pressure signal of the stenosis proximal side S p The blood pressure signal of the stenosis proximal side S p is a signal in which the pressure information periodically changes with the time information, and the length of one cycle of the change of the pressure information with the time information can be regarded as the length of one cardiac cycle. In the present embodiment, the cardiac cycle generally refers to the time experienced by the heart to contract and dilate once. In various embodiments, the blood pressure signal of the stenosis proximal side S p The blood pressure signal of the stenosis proximal side S p includes the blood pressure signals of a plurality of consecutive cardiac cycles.

[0044] In various embodiments, the distal pressure measurement instrument 20 can be introduced into the blood vessel and can perform pressure measurement at a predetermined position in the blood vessel. In various embodiments, the distal pressure measurement instrument 20 can be introduced into the blood vessel and placed near the stenosis lesion S, for example, placed at the stenosis distal side S d to obtain the blood pressure signal of the stenosis distal side S d (see Figure 2 ).

[0045] In various embodiments, the distal pressure measurement instrument 20 can include a pressure sensor 21 for obtaining the blood pressure signal, and a pushing tool 22 for pushing the pressure sensor 21 (see Figure 2 ). The pressure sensor 21 can be introduced into the blood vessel and can perform pressure measurement in the blood vessel, and the pressure sensor 21 can be arranged on the pushing tool 22, and the pushing tool 22 can extend along the blood vessel to the outside of the body (see Figure 2 ). In various embodiments, the pressure sensor 21 can be pushed by the pushing tool 22 to be placed at a predetermined position in the blood vessel, for example, placed at the stenosis distal side S d .

[0046] In various embodiments, as described above, the pressure sensor 21 can be introduced into the blood vessel and can perform pressure measurement in the blood vessel. In various embodiments, the pressure sensor 21 can be introduced into the blood vessel and placed at a predetermined position, for example, placed at the stenosis distal side S d to obtain the blood pressure signal of the stenosis distal side S d (see Figure 2 ).

[0047] In various embodiments, the pressure sensor 21 can be a pressure sensor for measuring fluid pressure, and the pressure sensor 21 can acquire a blood pressure signal by sensing the fluid pressure of the blood flow. In some examples, the pressure sensor 21 can be a resistive pressure sensor, a capacitive pressure sensor, a piezoelectric pressure sensor, an inductive pressure sensor, a thermoelectric pressure sensor, or an optoelectronic pressure sensor. In some examples, the pressure sensor 21 can be a pressure sensing device based on silicon. In some examples, the pressure sensor 21 can be a differential pressure sensor to reduce noise interference during signal transmission.

[0048] In some examples, the blood pressure signal acquired by the pressure sensor 21 can be transmitted to the outside of the body through a wired manner, for example, via a signal line (not shown) provided on the push tool. In other examples, the blood pressure signal acquired by the pressure sensor 21 can also be transmitted to the outside of the body through a wireless transmission manner, for example, Bluetooth, WIFI, or NFC.

[0049] In various embodiments, the pressure sensor 21 can perform pressure measurement within the blood vessel at a predetermined sampling frequency. In various embodiments, the pressure sensor 21 can continuously perform pressure measurement within the blood vessel at a predetermined sampling frequency. In some examples, the pressure sensor 21 can perform pressure measurement within the blood vessel at a sampling frequency of 100-500 times per second. For example, 100 times per second, 150 times per second, 200 times per second, 250 times per second, 300 times per second, 400 times per second, or 500 times per second. That is, the pressure sensor 21 can acquire 100-500 blood pressure signals representing the pressure within the blood vessel per second.

[0050] In some examples, the blood pressure signal acquired by the pressure sensor 21 can be an analog signal. In various embodiments, the blood pressure signal acquired by the pressure sensor 21 can include pressure information and time information. In various embodiments, a cardiac cycle can be acquired based on the blood pressure signal acquired by the pressure sensor 21. Specifically, the blood pressure signal acquired by the pressure sensor 21 can be a signal in which the pressure information periodically changes with the time information, and the length of one change cycle of the pressure information with the time information can be regarded as the length of one cardiac cycle. In various embodiments, the blood pressure signal acquired by the pressure sensor 21 can include blood pressure signals of a plurality of consecutive cardiac cycles.

[0051] In various embodiments, the signal processor 30 can receive and process the blood pressure signal acquired by the pressure sensor 21 to acquire the effective value of the pressure within the blood vessel. In various embodiments, the signal processor 30 can receive and process the blood pressure signal acquired by the distal pressure measurement apparatus 20 at the stenosis distal side S d to acquire the effective value of the pressure at the stenosis distal side S dan effective value of the blood pressure at the stenosis proximal side S p . In various embodiments, the signal processor 30 can further receive and process the blood pressure signal at the stenosis proximal side S p to obtain the mean pressure at the stenosis proximal side S d . In various embodiments, the signal processor 30 can obtain the effective value of the FFR based on the effective value of the blood pressure at the stenosis distal side S p and the mean pressure at the stenosis proximal side S

[0052] Figure 3 is a block diagram showing the signal processor 30 involved in the examples of the present disclosure. In various embodiments, the signal processor 30 can comprise a communication module 31 (see Figure 3 ). The communication module 31 can communicate with the pressure sensor 21 to receive the blood pressure signal obtained by the pressure sensor 21, such as the blood pressure signal at the stenosis distal side S d .

[0053] In some examples, the communication module 31 can be a wired communication module, such as a USB interface, an HDMI interface, an RS232 interface, etc., and the blood pressure signal obtained by the pressure sensor 21 can be transmitted to the signal processor 30 via a signal line provided in the push tool and the communication module 31. In other examples, the communication module 31 can be a wireless communication module, such as Bluetooth, WIFI, NFC, etc., and the blood pressure signal obtained by the pressure sensor 21 can be transmitted to the signal processor 30 in a wireless manner.

[0054] In various embodiments, the signal processor 30 can further comprise an analog-to-digital conversion module 32 (see Figure 3 ). The analog-to-digital conversion module 32 can convert the blood pressure signal obtained by the pressure sensor 21 (e.g., the blood pressure signal at the stenosis distal side S d ) from an analog signal to a digital signal that can be used to represent the pressure value.

[0055] Figure 4 is a diagram showing the blood pressure signal sampling waveform involved in the examples of the present disclosure.

[0056] In some examples, the signal processor 30 can further comprise a waveform shaping module 33 (see Figure 3 ). The waveform shaping module 33 can shape the blood pressure signal obtained by the pressure sensor 21, which comprises a plurality of consecutive cardiac cycles, into a blood pressure signal sampling waveform showing the change of the intravascular pressure over time. Specifically, given that the blood pressure signal obtained by the pressure sensor 21 comprises pressure information and time information, the waveform shaping module 33 can establish a coordinate system with time as the horizontal axis and pressure as the vertical axis, and label the blood pressure signal obtained by the pressure sensor 21 (e.g., the blood pressure signal at the stenosis distal side S dcorresponding to the blood pressure signal) to form a blood pressure signal sampling waveform of pressure change over time comprising a plurality of cardiac cycles (see Figure 4 ).

[0057] In some examples, the signal processor 30 can further comprise a reference obtaining module 34. The reference obtaining module 34 can obtain a reference peak value and a reference valley value based on the blood pressure signal sampling waveform.

[0058] The reference obtaining module 34 obtaining the reference peak value and the reference valley value can comprise: selecting a continuous cycle signal waveform comprising a predetermined number of cardiac cycles in the blood pressure signal sampling waveform; judging whether a fluctuation of the peak values of the continuous cycle signal waveform is not greater than a first threshold value; judging whether a fluctuation of the valley values of the continuous cycle signal waveform is not greater than a second threshold value; if the fluctuation of the peak values of the continuous cycle signal waveform is not greater than the first threshold value and the fluctuation of the valley values of the continuous cycle signal waveform is not greater than the second threshold value, calculating effective peak values and effective valley values of the continuous cycle signal waveform; obtaining the reference peak value and the reference valley value based on the effective peak values and the effective valley values.

[0059] In various embodiments, if the fluctuation of the peak values of the continuous cycle signal waveform is greater than the first threshold value or the fluctuation of the valley values of the continuous cycle signal waveform is greater than the second threshold value, the continuous cycle signal waveform comprising the predetermined number of cardiac cycles can be reselected in the blood pressure signal sampling waveform.

[0060] In some examples, the reference obtaining module 34 obtaining the reference peak value and the reference valley value can further comprise: judging whether a ratio of an interval of adjacent peak values of the continuous cycle signal waveform to a cardiac cycle falls into a first interval, for example, 0.8-1.2; judging whether a ratio of an interval of adjacent valley values of the continuous cycle signal waveform to a cardiac cycle falls into a second interval, for example, 0.8-1.2; if the ratio of the interval of any adjacent peak values of the continuous cycle signal waveform to the cardiac cycle falls into the first interval and the ratio of the interval of any adjacent valley values of the continuous cycle signal waveform to the cardiac cycle falls into the second interval, calculating the effective peak values and the effective valley values of the continuous cycle signal waveform; if the ratio of the interval of any adjacent peak values of the continuous cycle signal waveform to the cardiac cycle does not fall into the first interval or the ratio of the interval of any adjacent valley values of the continuous cycle signal waveform to the cardiac cycle does not fall into the second interval, reselecting the continuous cycle signal waveform comprising the predetermined number of cardiac cycles.

[0061] Figure 5 is a schematic diagram showing a continuous cycle signal waveform involved in the examples of the present disclosure.

[0062] In various embodiments, the continuous cycle signal waveform comprising the predetermined number of cardiac cycles can be defined as a signal waveform corresponding to a continuous time in the blood pressure signal sampling waveform, and the continuous time can comprise the predetermined number of cardiac cycles (see Figure 5). In some examples, the predetermined number can be 1-12, such as 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, or 12.

[0063] In various embodiments, peak fluctuation can be defined as the relative change between adjacent peaks in a continuous periodic signal waveform. Figure 5 In the embodiment shown, the peaks in the continuous periodic signal waveform include a first peak P1, a second peak P2, and a third peak P3. The fluctuation between the first peak P1 and the second peak P2 can be defined as: In some examples, the first threshold can be 0.05 to 0.30, for example 0.05, 0.06, 0.07, 0.08, 0.09, 0.10, 0.11, 0.12, 0.13, 0.14, 0.15, 0.16, 0.17, 0.18, 0.19, 0.20, 021, 0.22, 0.23, 0.24, 0.25, 0.26, 0.27, 0.28, 0.29 or 0.30.

[0064] In various embodiments, the fluctuation of valley values ​​can be defined as the relative change between adjacent valley values ​​in a continuous periodic signal waveform. Figure 5 In the embodiment shown, the valley values ​​in the continuous periodic signal waveform include a first valley value V1, a second valley value V2, and a third valley value V3. The fluctuation between the first valley value V1 and the second valley value V2 can be defined as: In some examples, the second threshold can be 0.05 to 0.30, for example 0.05, 0.06, 0.07, 0.08, 0.09, 0.10, 0.11, 0.12, 0.13, 0.14, 0.15, 0.16, 0.17, 0.18, 0.19, 0.20, 0.21, 0.22, 0.23, 0.24, 0.25, 0.26, 0.27, 0.28, 0.29 or 0.30.

[0065] In some examples, if the fluctuation of any adjacent peak values ​​of the continuous periodic signal waveform is not greater than a first threshold and the fluctuation of any adjacent valley values ​​of the continuous periodic signal waveform is not greater than a second threshold, then the effective peak value may be the average value or median value of the peak values ​​of the continuous periodic signal waveform. In some examples, if the fluctuation of the peak values ​​of the continuous periodic signal waveform is not greater than a first threshold and the fluctuation of the valley values ​​of the continuous periodic signal waveform is not greater than a second threshold, then the effective valley value may be the average value or median value of the valley values ​​of the continuous periodic signal waveform.

[0066] For example, Figure 5 In the embodiment shown, if the fluctuation of P1, P2, and P3 is not greater than the first threshold and the fluctuation of V1, V2, and V3 is not greater than the second threshold, then the effective peak value P eIt can be the average value of P1, P2, and P3 (i.e., ) or the median value of P1, P2, P3, effective valley value V e It can be the average value of V1, V2, and V3 (i.e., ) or the median value of V1, V2, and V3.

[0067] In some examples, the reference peak value can be obtained based on the effective peak value and the difference between the effective peak value and the effective valley value. In some examples, the reference peak value can be the sum of the effective peak value and the difference between the effective peak value and the effective valley value multiplied by the first factor f1. Figure 5 In the embodiment shown, the reference peak value P r =P e +(P e -V e )×f1. In some examples, the first factor f1 can be 0.05 to 0.30, for example, 0.05, 0.06, 0.07, 0.08, 0.09, 0.10, 0.11, 0.12, 0.13, 0.14, 0.15, 0.16, 0.17, 0.18, 0.19, 0.20, 0.21, 0.22, 023, 0.24, 0.25, 026, 0.27, 0.28, 0.29, or 0.30.

[0068] In some examples, the reference valley value can be obtained based on the effective valley value and the difference between the effective peak value and the effective valley value. In some examples, the reference valley value can be the difference between the effective valley value and the difference between the effective peak value and the effective valley value multiplied by the second factor f2. Figure 5 In the embodiment shown, the reference valley value V r =V e -(P e -V e )×f2. In some examples, the second factor f2 can be 0.05 to 0.30, for example, 0.05, 0.06, 0.07, 0.08, 0.09, 0.10, 0.11, 0.12, 0.13, 0.14, 0.15, 0.16, 0.17, 0.18, 0.19, 0.20, 0.21, 0.22, 023, 0.24, 0.25, 0.26, 0.27, 0.28, 0.29, or 0.30.

[0069] In some examples, the signal processor 30 may further include a normal identification module 35. The normal identification module 35 may identify and mark normal pressure values ​​in the blood pressure signal sampling waveform based on reference peak values ​​and reference valley values.

[0070] The normal recognition module 35 marks the normal pressure value in the blood pressure signal sampling waveform, which may include: determining whether each pressure value in the blood pressure signal sampling waveform falls within the range of the reference peak value and the reference valley value, for example, Figure 5 In the embodiment shown, the normal recognition module 35 can determine whether each pressure value in the blood pressure signal sampling waveform is within the reference peak value P r Compared with the benchmark valley value V r If the pressure value falls within the range of the reference peak value and the reference valley value, the pressure value is marked as normal.

[0071] In some examples, the normal identification module 35 marking a normal pressure value in the blood pressure signal sampling waveform may further include: if the pressure value does not fall within the range of a reference peak value and a reference valley value, marking the pressure value as abnormal.

[0072] In some examples, the range of the reference peak value and the reference valley value may include the reference peak value and the reference valley value. In other examples, the range of the reference peak value and the reference valley value may not include the reference peak value and the reference valley value.

[0073] In some examples, the signal processor 30 may further include a blood pressure effective value acquisition module 36. The blood pressure effective value acquisition module 36 may acquire the effective value of the intravascular pressure corresponding to a cardiac cycle (e.g., the S value on the distal side of the stenosis) based on the pressure value marked as normal in a single-cycle signal waveform including one cardiac cycle (hereinafter, the current cardiac cycle is used as an example for explanation). d effective value of blood pressure).

[0074] The blood pressure effective value acquisition module 36 obtains the effective value of the intravascular pressure by: selecting a single-cycle signal waveform including the current cardiac cycle in the blood pressure signal sampling waveform; calculating the ratio of the number of pressure values ​​marked as normal to the number of all pressure values ​​in the single-cycle signal waveform; if the ratio is not less than a third threshold value, obtaining the effective value of the intravascular pressure corresponding to the current cardiac cycle based on the pressure value marked as normal in the single-cycle signal waveform.

[0075] In various embodiments, a single-cycle signal waveform including the current cardiac cycle can be defined as a signal waveform corresponding to the current cardiac cycle in the blood pressure signal sampling waveform, and the single-cycle signal waveform can be a signal waveform between one trough to the next trough in the blood pressure signal sampling waveform. In some examples, the third threshold value can be 0.70 to 1.0, such as 0.70, 0.71, 0.72, 0.73, 0.74, 0.75, 0.76, 0.77, 0.78, 0.79, 0.80, 0.81, 0.82, 0.83, 0.84, 0.85, 0.86, 0.87, 0.88, 0.89, 0.90, 0.91, 0.92, 0.93, 0.94, 0.95, 0.96, 0.97, 0.98, 0.99, or 1.

[0076] In some examples, in the single-cycle signal waveform of the current cardiac cycle, if the ratio of the number of pressure values marked as normal to the number of all pressure values is not less than the third threshold value, the current cardiac cycle is marked as valid, and the average value of the pressure values marked as normal in the single-cycle signal waveform of the current cardiac cycle is used as the valid value of the intravascular pressure of the current cardiac cycle. In other examples, the average value of all pressure values marked as normal in the single-cycle signal waveform of the current cardiac cycle and at least one (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, or 12) cardiac cycle marked as valid located before the current cardiac cycle and closest to the current cardiac cycle can also be used as the valid value of the intravascular pressure of the current cardiac cycle (e.g., S d valid value of the blood pressure). In other examples, the valid value of the current cardiac cycle can also be obtained based on the average value of all pressure values marked as normal in the single-cycle signal waveform of the current cardiac cycle and the valid values of at least one (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, or 12) cardiac cycle marked as valid located before the current cardiac cycle and closest to the current cardiac cycle, such as the result obtained by averaging them.

[0077] In some examples, in the single-cycle signal waveform of the current cardiac cycle, if the ratio of the number of pressure values marked as normal to the number of all pressure values is less than the third threshold value, the current cardiac cycle is marked as invalid, and the average value of all pressure values marked as normal in the single-cycle signal waveform of at least one (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, or 12) cardiac cycle marked as valid located before the current cardiac cycle and closest to the current cardiac cycle is used as the valid value of the intravascular pressure of the current cardiac cycle (e.g., S dIn other examples, the effective value of the current cardiac cycle may be obtained based on the effective value corresponding to at least one cardiac cycle (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, or 12) that is located before the current cardiac cycle and closest to the current cardiac cycle and marked as effective, for example, by averaging the values.

[0078] In some examples, the signal processor 30 may further include an FFR effective value acquisition module 37. The FFR effective value acquisition module 37 may be based on the stenosis proximal side S p The blood pressure signal and one cardiac cycle (hereinafter, the current cardiac cycle is used as an example for explanation) corresponding to the distal side of the stenosis S d The effective value of blood pressure is used to obtain the effective value of FFR during the cardiac cycle.

[0079] The FFR effective value acquisition module 37 acquires the effective value of FFR in the current cardiac cycle, which may include: p The blood pressure signal is used to obtain the S proximal side of the stenosis in the current cardiac cycle. p Get the mean pressure of the distal side of the stenosis in the current cardiac cycle d The effective value of blood pressure; calculate the S distal to the stenosis in the current cardiac cycle d The effective value of blood pressure and S p The ratio of the mean pressure to the mean pressure is used as the effective value of FFR in the current cardiac cycle.

[0080] FIG. 6 is a schematic diagram showing an FFR displayed by a display device according to an example of the present disclosure.

[0081] in, Figure 6A is a schematic diagram showing an unprocessed FFR displayed by a display device according to an example of the present disclosure. Figure 6B FIG. 1 is a schematic diagram showing an effective value of FFR displayed by a display device according to an example of the present disclosure.

[0082] In various embodiments, as described above, the FFR measurement system 1 may further include a display device 40. The display device 40 may display the stenosis proximal side S p Blood pressure signal, untreated stenosis distal side S d Blood pressure signal, processed distal stenosis S d blood pressure signal, unprocessed FFR value or effective FFR value (see Figure 6A and Figure 6B ).

[0083] In some examples, the display device 40 may have a first display area 41 and a second display area 42 (see Figure 6A and Figure 6B). The first display area 41 can be used to display the blood pressure signal at the distal side S d of the stenosis, for example, to display a blood pressure signal sample waveform including a plurality of cardiac cycles of the intravascular pressure over time. The second display area 42 can be used to display the value of the FFR. In some examples, the first display area 41 and the second display area 42 can share the same horizontal axis (i.e., time axis).

[0084] In some examples, in the blood pressure signal sample waveform, if there is a pressure value marked as abnormal, the first display area 41 can display the uncorrected waveform, and the second display area 42 can display the unprocessed value of the FFR (see Figure 6A ).

[0085] In some examples, in the blood pressure signal sample waveform, if there is a pressure value marked as abnormal, the first display area 41 can display the uncorrected waveform, and the second display area can display the valid value of the FFR (see Figure 6B ). In this case, it can help the physician to know the valid value of the FFR, and it can also facilitate the physician to find the apposition of the distal pressure measurement instrument 20.

[0086] In other examples, in the blood pressure signal sample waveform, if there is a pressure value marked as abnormal, the first display area 41 can correct the waveform of each cardiac cycle based on the valid value of the intravascular pressure corresponding to the cardiac cycle, and display the corrected waveform, and the second display area 42 can display the valid value of the FFR.

[0087] In various embodiments, the FFR measurement system 1 can also not include the proximal pressure measurement instrument 10, thereby providing a pressure measurement system for pressure measurement in a blood vessel. In various embodiments, the pressure measurement system can include the distal pressure measurement instrument 20 related to the present disclosure and the signal processor 30 related to the present disclosure. The distal pressure measurement instrument 20 can be introduced into a blood vessel and can acquire a blood pressure signal at a predetermined position in the blood vessel, and the signal processor 30 can process the blood pressure signal acquired by the distal pressure measurement instrument 20 to obtain a valid value of the intravascular pressure at the predetermined position. In various embodiments, the pressure measurement system can also include the display device 40 related to the present disclosure, which can display the valid value of the intravascular pressure.

[0088] In various embodiments, the FFR measurement system 1 can also not include the proximal pressure measurement instrument 10 and the distal pressure measurement instrument 20, thereby providing a signal processing system for intravascular pressure measurement or a signal processing system for FFR measurement. In various embodiments, the signal processing system can process the blood pressure signals in the blood vessel acquired by other devices to obtain the effective value of the intravascular pressure. In various embodiments, the signal processing system can process the blood pressure signals in the blood vessel acquired by other devices to obtain the effective value of the FFR. In various embodiments, the signal processing system can include the signal processor 30 involved in the present disclosure and process the blood pressure signals in the blood vessel acquired by other devices through the signal processor 30. In various embodiments, the signal processing system can also include the display device 40 involved in the present disclosure and display the effective value of the intravascular pressure or the effective value of the FFR through the display device 40.

[0089] FIG. 7 is a flowchart illustrating a signal processing method for FFR measurement involved in an example of the present disclosure. In which, Figure 7A is a whole flowchart illustrating a signal processing method for FFR measurement involved in an example of the present disclosure, Figure 7B is a flowchart illustrating a process of obtaining reference peak value and reference valley value involved in an example of the present disclosure. In the following, Figure 7A and Figure 7B , the signal processing method for FFR measurement involved in an example of the present disclosure is described in detail.

[0090] Various embodiments of the present disclosure provide a signal processing method for FFR measurement (see Figure 7A ), which can include: acquiring blood pressure signals of a stenosis proximal side S p and blood pressure signals of a stenosis distal side S d ; wave shaping the blood pressure signals of the stenosis distal side S d to obtain a blood pressure signal sampling waveform including intravascular pressure changes over time of multiple cardiac cycles; obtaining reference peak value and reference valley value based on the blood pressure signal sampling waveform; identifying and marking normal pressure values in the blood pressure signal sampling waveform based on the reference peak value and the reference valley value; obtaining the effective value of the blood pressure of the stenosis distal side S d corresponding to a single cycle signal waveform including one cardiac cycle based on the pressure values marked as normal; and obtaining the effective value of the FFR in the corresponding cardiac cycle based on the blood pressure signals of the stenosis proximal side S p and the effective value of the blood pressure of the stenosis distal side S d in one cardiac cycle.

[0091] In the signal processing method for FFR measurement involved in an example of the present disclosure, the blood pressure signals of the stenosis proximal side S p and the blood pressure signals of the stenosis distal side Sd blood pressure signal of the stenosis distal side S p The blood pressure signal of the stenosis distal side S d The blood pressure signal of the stenosis distal side S p The blood pressure signal of the stenosis distal side S

[0092] In the signal processing method of FFR measurement involved in the examples of the present disclosure, the blood pressure signal of the stenosis distal side S d is wave-shaped to obtain a blood pressure signal sampling waveform including the change of intravascular pressure with time of multiple cardiac cycles. In various embodiments, it can include: receiving the blood pressure signal of the stenosis distal side S d ; converting the blood pressure signal of the stenosis distal side S d from an analog signal to a digital signal that can be used to represent a pressure value; marking the coordinate points corresponding to the blood pressure signal of the stenosis distal side S d one by one in the coordinate system, with time represented by the horizontal axis and pressure represented by the vertical axis; forming a blood pressure signal sampling waveform including the change of pressure with time of multiple cardiac cycles in the coordinate system (see Figure 4 ). In various embodiments, the analog-digital conversion module 32 involved in the examples of the present disclosure can convert the blood pressure signal of the stenosis distal side S d from an analog signal to a digital signal that can be used to represent a pressure value. In various embodiments, the wave-shaping module 33 involved in the examples of the present disclosure can form a blood pressure signal sampling waveform including the change of pressure with time of multiple cardiac cycles.

[0093] In the signal processing method of FFR measurement involved in the examples of the present disclosure, the reference peak value and the reference valley value are obtained based on the blood pressure signal sampling waveform (see Figure 7B ). In various embodiments, it can include: selecting a continuous cycle signal waveform including a predetermined number of cardiac cycles in the blood pressure signal sampling waveform; judging whether the fluctuation of the peak value of the continuous cycle signal waveform is not greater than a first threshold value; judging whether the fluctuation of the valley value of the continuous cycle signal waveform is not greater than a second threshold value; if the fluctuation of the peak value of the continuous cycle signal waveform is not greater than the first threshold value and the fluctuation of the valley value of the continuous cycle signal waveform is not greater than the second threshold value, obtaining an effective peak value and an effective valley value of the continuous cycle signal waveform; obtaining the reference peak value and the reference valley value based on the effective peak value and the effective valley value. In various embodiments, the reference obtaining module 34 involved in the examples of the present disclosure can obtain the reference peak value and the reference valley value.

[0094] In the signal processing method for FFR measurement involved in the examples of the present disclosure, normal pressure values in the blood pressure signal sampling waveform are identified and marked based on the reference peak value and the reference valley value. In various embodiments, it can include: determining whether each pressure value in the blood pressure signal sampling waveform falls within the range of the reference peak value and the reference valley value; if the pressure value falls within the range of the reference peak value and the reference valley value, marking the pressure value as normal. In some examples, if the pressure value does not fall within the range of the reference peak value and the reference valley value, marking the pressure value as abnormal. In various embodiments, the normal identification module 35 involved in the examples of the present disclosure can identify and mark the normal pressure values in the blood pressure signal sampling waveform.

[0095] In the signal processing method for FFR measurement involved in the examples of the present disclosure, based on the pressure values marked as normal in the single-cycle signal waveform including one cardiac cycle (hereinafter, taking the current cardiac cycle as an example for description), the effective value of the intravascular pressure corresponding to the cardiac cycle is obtained (for example, the effective value of the blood pressure on the distal side S d of the stenosis). In various embodiments, it can include: in the blood pressure signal sampling waveform, selecting a single-cycle signal waveform including the current cardiac cycle; in the single-cycle signal waveform, calculating the ratio of the number of pressure values marked as normal to the number of all pressure values; if the ratio is not less than a third threshold value, obtaining the effective value of the intravascular pressure corresponding to the current cardiac cycle based on the pressure values marked as normal in the single-cycle signal waveform. In various embodiments, the effective blood pressure value obtaining module 36 involved in the examples of the present disclosure can obtain the effective value of the intravascular pressure corresponding to the current cardiac cycle (for example, the effective value of the blood pressure on the distal side S d of the stenosis).

[0096] In the signal processing method for FFR measurement involved in the examples of the present disclosure, based on the blood pressure signal on the proximal side S p of the stenosis and the effective value of the blood pressure on the distal side S d of the stenosis within one cardiac cycle (hereinafter, taking the current cardiac cycle as an example for description), the effective value of FFR within the current cardiac cycle is obtained. In various embodiments, it can include: obtaining the average pressure on the proximal side S p of the stenosis within the current cardiac cycle based on the blood pressure signal on the proximal side S p of the stenosis; obtaining the effective value of the blood pressure on the distal side S d of the stenosis within the current cardiac cycle; calculating the ratio of the effective value of the blood pressure on the distal side S d of the stenosis within the current cardiac cycle to the average pressure on the proximal side S p of the stenosis, and taking the ratio as the effective value of FFR within the current cardiac cycle. In various embodiments, the FFR effective value obtaining module 37 involved in the examples of the present disclosure can obtain the effective value of FFR within the current cardiac cycle.

[0097] Figure 8 is a flowchart showing a signal processing method of intravascular pressure measurement involved in the present disclosure example. Hereinafter, the signal processing method of intravascular pressure measurement involved in the present disclosure example will be described in detail. Figure 8

[0098] Various embodiments of the present disclosure provide a signal processing method of intravascular pressure measurement (see Figure 8 ), which can include: acquiring a blood pressure signal of a predetermined position in a blood vessel; wave shaping the blood pressure signal of the predetermined position to acquire a blood pressure signal sampling waveform including a plurality of cardiac cycles of intravascular pressure change over time; acquiring a reference peak value and a reference valley value based on the blood pressure signal sampling waveform; identifying and marking normal pressure values in the blood pressure signal sampling waveform based on the reference peak value and the reference valley value; and acquiring an effective value of intravascular pressure corresponding to one cardiac cycle based on the pressure values marked as normal in a single cycle signal waveform including the cardiac cycle.

[0099] In the signal processing method of intravascular pressure measurement involved in the present disclosure example, a blood pressure signal of a predetermined position in a blood vessel is acquired. In some examples, the blood pressure signal of the predetermined position can be acquired by the distal pressure measurement instrument 20 involved in the present disclosure example. In various embodiments, a cardiac cycle can be acquired based on the blood pressure signal of the predetermined position.

[0100] In the signal processing method of intravascular pressure measurement involved in the present disclosure example, the blood pressure signal of the predetermined position is wave shaped to acquire a blood pressure signal sampling waveform including a plurality of cardiac cycles of intravascular pressure change over time. In various embodiments, it can include: receiving the blood pressure signal of the predetermined position; converting the blood pressure signal of the predetermined position from an analog signal to a digital signal that can be used to represent a pressure value; labeling coordinate points corresponding to the blood pressure signal of the predetermined position one by one in a coordinate system with the time represented by the horizontal axis and the pressure represented by the vertical axis; and forming a blood pressure signal sampling waveform including a plurality of cardiac cycles of pressure change over time in the coordinate system (see Figure 4 ). In various embodiments, the blood pressure signal of the predetermined position can be converted from an analog signal to a digital signal that can be used to represent a pressure value by the analog-digital conversion module 32 involved in the present disclosure example. In various embodiments, a blood pressure signal sampling waveform including a plurality of cardiac cycles of pressure change over time can be formed by the wave shaping module 33 involved in the present disclosure example.

[0101] ​In the signal processing method for intravascular pressure measurement according to the examples of the present disclosure, the reference peak value and the reference valley value are obtained based on the blood pressure signal sampling waveform. In various embodiments, it can include: in the blood pressure signal sampling waveform, selecting a continuous period signal waveform including a predetermined number of cardiac cycles; determining whether the fluctuation of the peak value of the continuous period signal waveform is not greater than a first threshold value; determining whether the fluctuation of the valley value of the continuous period signal waveform is not greater than a second threshold value; if the fluctuation of the peak value of the continuous period signal waveform is not greater than the first threshold value and the fluctuation of the valley value of the continuous period signal waveform is not greater than the second threshold value, calculating an effective peak value and an effective valley value of the continuous period signal waveform; and obtaining the reference peak value and the reference valley value based on the effective peak value and the effective valley value. In various embodiments, the reference obtaining module 34 according to the examples of the present disclosure can obtain the reference peak value and the reference valley value.

[0102] In the signal processing method for intravascular pressure measurement according to the examples of the present disclosure, based on the reference peak value and the reference valley value, the normal pressure values in the blood pressure signal sampling waveform are identified and marked. In various embodiments, it can include: determining whether each pressure value in the blood pressure signal sampling waveform falls within the range of the reference peak value and the reference valley value; if the pressure value falls within the range of the reference peak value and the reference valley value, marking the pressure value as normal. In some examples, if the pressure value does not fall within the range of the reference peak value and the reference valley value, marking the pressure value as abnormal. In various embodiments, the normal identification module 35 according to the examples of the present disclosure can identify and mark the normal pressure values in the blood pressure signal sampling waveform.

[0103] In the signal processing method for intravascular pressure measurement according to the examples of the present disclosure, based on the pressure values marked as normal in the single period signal waveform including one cardiac cycle (hereinafter, taking the current cardiac cycle as an example for description), the effective value of the intravascular pressure corresponding to the cardiac cycle is obtained. In various embodiments, it can include: in the blood pressure signal sampling waveform, selecting a single period signal waveform including the current cardiac cycle; in the single period signal waveform, calculating the ratio of the number of pressure values marked as normal to the number of all pressure values; if the ratio is not less than a third threshold value, obtaining the effective value of the intravascular pressure corresponding to the current cardiac cycle based on the pressure values marked as normal in the single period signal waveform. In various embodiments, the blood pressure effective value obtaining module 36 according to the examples of the present disclosure can obtain the effective value of the intravascular pressure corresponding to the current cardiac cycle.

[0104] According to the present disclosure, the adverse effects of signal abnormalities caused by wall attachment during intravascular pressure measurement can be effectively reduced.

[0105] Although the present disclosure has been specifically shown and described with reference to the accompanying drawings and examples, it will be understood by those skilled in the art that the above description is not in any way limiting to the present disclosure. Those skilled in the art can make modifications and changes to the present disclosure as needed without departing from the essential spirit and scope of the present disclosure, and such modifications and changes fall within the scope of the present disclosure.

Claims

1. A blood pressure monitoring system, characterized by, The blood pressure monitoring system is used to process blood pressure signals, and the processing includes: obtaining a blood pressure signal sampling waveform including a plurality of cardiac cycles in which the intravascular pressure changes with time; selecting a continuous cycle signal waveform including a predetermined number of cardiac cycles from the blood pressure signal sampling waveform, judging whether the fluctuation of the peak value of the continuous cycle signal waveform is not greater than a first threshold value, and judging whether the fluctuation of the valley value of the continuous cycle signal waveform is not greater than a second threshold value; if the fluctuation of the peak value of the continuous cycle signal waveform is not greater than the first threshold value and the fluctuation of the valley value of the continuous cycle signal waveform is not greater than the second threshold value, or judging whether the ratio of the interval between adjacent peak values ​​of the continuous cycle signal waveform and the cardiac cycle falls below Enter the first interval, and determine whether the ratio of the interval between adjacent valley values ​​of the continuous period signal waveform to the cardiac cycle falls into the second interval. If the ratio of the interval between adjacent peak values ​​of the continuous period signal waveform to the cardiac cycle falls into the first interval and the ratio of the interval between adjacent valley values ​​of the continuous period signal waveform to the cardiac cycle falls into the second interval, then calculate the effective peak value and the effective valley value of the continuous period signal waveform, wherein the effective peak value is the average value or median value of the peak value of the continuous period signal waveform, and the effective valley value is the average value or median value of the valley value of the continuous period signal waveform; obtain a reference peak value and a reference valley value based on the effective peak value and the effective valley value, wherein the reference peak value satisfies the formula: P r =P e +(P e -V e )×f1,P r represents the reference peak value, P e represents the effective peak value, V e represents the effective valley value, f1 represents the first factor, and the reference valley value satisfies the formula: V r =V e -(P e -V e )×f2,V r represents the reference valley value, f2 represents the second factor; based on the reference peak value and the reference valley value, the normal pressure value in the blood pressure signal sampling waveform is identified and marked; and based on the pressure value marked as normal in a single-cycle signal waveform including one cardiac cycle in the blood pressure signal sampling waveform, the effective value of the intravascular pressure corresponding to the single-cycle signal waveform is obtained. 2.The blood pressure monitoring system of claim 1, wherein, if a ratio of a number of the pressure values labeled as normal to a number of all the pressure values in the single-cycle signal waveform is not less than a third threshold, an effective value of the intravascular pressure corresponding to the single-cycle signal waveform is calculated based on the pressure values labeled as normal in the single-cycle signal waveform, wherein the pressure values labeled as normal are the pressure values falling within a range of the reference peak value and the reference valley value. 3.The blood pressure monitoring system of claim 2, wherein, if the ratio of the number of the pressure values labeled as normal to the number of all the pressure values is less than the third threshold, the cardiac cycle corresponding to the single-cycle signal waveform is labeled as invalid, and the effective value of the intravascular pressure corresponding to the single-cycle signal waveform is obtained based on at least one cardiac cycle labeled as valid closest to the single-cycle signal waveform. 4.The blood pressure monitoring system of claim 1, wherein, the fluctuation of the peak values is a relative change between adjacent peak values in the continuous-cycle signal waveform, and the fluctuation of the valley values is a relative change between adjacent valley values in the continuous-cycle signal waveform. 5.The blood pressure monitoring system of claim 1, wherein, if the fluctuation of the peak values of the continuous-cycle signal waveform is greater than the first threshold or the fluctuation of the valley values of the continuous-cycle signal waveform is greater than the second threshold, the selection of the continuous-cycle signal waveform is re-performed. 6.The blood pressure monitoring system of claim 1, wherein, the first factor is 0.05 to 0.30, and the second factor is 0.05 to 0.

30.

7. A signal processing method characterized by, comprising: obtaining a blood pressure signal sampling waveform including changes of intravascular pressure over time including a plurality of cardiac cycles; In the blood pressure signal sampling waveform, a continuous period signal waveform including a predetermined number of cardiac cycles is selected, it is judged whether the fluctuation of the peak value of the continuous period signal waveform is not greater than a first threshold value, and it is judged whether the fluctuation of the valley value of the continuous period signal waveform is not greater than a second threshold value, if the fluctuation of the peak value of the continuous period signal waveform is not greater than the first threshold value and the fluctuation of the valley value of the continuous period signal waveform is not greater than the second threshold value, the effective peak value and the effective valley value of the continuous period signal waveform are calculated, wherein the effective peak value is the average value or the median value of the peak value of the continuous period signal waveform, and the effective valley value is the average value or the median value of the valley value of the continuous period signal waveform; the reference peak value and the reference valley value are obtained based on the effective peak value and the effective valley value, wherein the reference peak value satisfies the formula: P r =P e +(P e -V e )×f1, P r represents the reference peak value, P e represents the effective peak value, V e represents the effective valley value, and f1 represents the first factor, the reference valley value satisfies the formula: V r =V e -(P e -V e )×f2, V r represents the reference valley value, and f2 represents the second factor; the normal pressure value in the blood pressure signal sampling waveform is identified and marked based on the reference peak value and the reference valley value; and the effective value of the intravascular pressure corresponding to the single period signal waveform is obtained based on the single period signal waveform including one cardiac cycle in the blood pressure signal sampling waveform and the pressure value marked as normal. 8.The signal processing method of claim 7, wherein, if a ratio of a number of the pressure values labeled as normal to a number of all the pressure values in the single-cycle signal waveform is not less than a third threshold, an effective value of the intravascular pressure corresponding to the single-cycle signal waveform is calculated based on the pressure values labeled as normal in the single-cycle signal waveform, wherein the pressure values labeled as normal are the pressure values falling within a range of the reference peak value and the reference valley value.

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