Reference acquisition method and reference acquisition module for identifying normal pressure values

Abstract

The present disclosure describes a baseline acquisition method and a baseline acquisition module for identifying normal pressure values. The baseline acquisition method includes: acquiring a blood pressure signal sampling waveform including a plurality of cardiac cycles, which shows changes in intravascular pressure over time; selecting a continuous cycle signal waveform including a predetermined number of cardiac cycles from the blood pressure signal sampling waveform; determining whether the fluctuation of the peak value of the continuous cycle signal waveform is no greater than a first threshold; and determining whether the fluctuation of the valley value of the continuous cycle signal waveform is no greater than a second threshold; if the fluctuation of the peak value of the continuous cycle signal waveform is no greater than the first threshold and the fluctuation of the valley value of the continuous cycle signal waveform is no greater than the second threshold, calculating the effective peak value and the effective valley value of the continuous cycle signal waveform, wherein the effective peak value is the average value or median value of the peak value of the continuous cycle signal waveform, and the effective valley value is the average value or median value of the valley value of the continuous cycle signal waveform; and obtaining a baseline peak value and a baseline valley value based on the effective peak value and the effective valley value. According to the present disclosure, the adverse effects of signal abnormalities caused by wall adhesion can be effectively reduced.

Description

[0001] This application is a divisional application of the patent application with application date of December 31, 2020, application number 2020116420319, and invention name: Intravascular Pressure Measurement System. Technical Field

[0002] The present disclosure relates to a reference acquisition method and a reference acquisition module for identifying a normal pressure value. Background Art

[0003] For many cardiovascular diseases, such as coronary heart disease, vascular stenosis (such as vascular stenosis caused by vascular plaques) can affect blood supply and cause great harm to patients. Currently, percutaneous coronary intervention (PCI) is a relatively effective treatment for this type of disease. In traditional methods, doctors usually use coronary angiography to visually assess the degree of stenosis of stenosis to determine whether to perform interventional treatment. However, this traditional method makes it difficult for doctors to accurately assess the impact of stenosis on blood supply, which may lead to inappropriate treatment.

[0004] In recent years, in order to more accurately determine whether a patient truly requires interventional treatment, the use of Fractional Flow Reverse (FFR) to assess the impact of stenotic lesions on blood supply has been increasingly used and promoted. FFR is defined as the ratio of the maximum blood flow that can be obtained by the myocardial area supplied by a coronary artery in the presence of a stenotic lesion to the maximum blood flow that the same area can theoretically obtain under normal circumstances. To calculate the FFR of a given stenosis in a coronary artery, it is necessary to measure the mean pressure (Pd) on the distal side of the stenosis (e.g., downstream of the stenosis, away from the aorta) and the mean pressure (Pa) on the proximal side of the stenosis (e.g., upstream of the stenosis, close to the aorta).

[0005] Currently, intravascular pressure is typically measured by placing a pressure measuring device at a predetermined location within the blood vessel, for example, by measuring the mean pressure (Pd) distal to a stenosis, thereby measuring FFR. However, during these pressure measurements, the pressure measuring device may become attached to the vessel wall, potentially resulting in abnormal blood pressure signals. Summary of the Invention

[0006] The present disclosure is proposed in view of the above-mentioned state of the prior art, and its purpose is to provide a signal processing method for measuring intravascular pressure that can effectively reduce the adverse effects of signal abnormalities caused by wall adhesion.

[0007] To this end, the present disclosure provides a signal processing method for measuring intravascular pressure, characterized in that a pressure measuring device is used to perform pressure measurement at a predetermined position in a blood vessel at a predetermined sampling frequency to obtain a blood pressure signal sampling waveform including a plurality of cardiac cycles in which the intravascular pressure changes with time. Among the blood pressure signal sampling waveforms, a continuous periodic signal waveform including a predetermined number of cardiac cycles is selected to determine whether the fluctuation of the peak value of the continuous periodic signal waveform is not greater than a first threshold value, and to determine whether the fluctuation of the valley value of the continuous periodic signal waveform is not greater than a second threshold value. 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, then the method is calculated. Calculate the effective peak value and the effective valley value of the continuous cycle signal waveform, obtain the reference peak value and the reference valley value based on the effective peak value and the effective valley value, determine 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, mark the pressure value as normal, and in the blood pressure signal sampling waveform, select a single-cycle signal waveform including one cardiac cycle, in the single-cycle 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 a third threshold value, then calculate the effective value of the intravascular pressure corresponding to the single-cycle signal waveform based on the pressure value marked as normal in the single-cycle signal waveform.

[0008] In the signal processing method disclosed herein, a pressure measuring device is used to obtain a blood pressure signal sampling waveform within a blood vessel, including a temporal variation of intravascular pressure over multiple cardiac cycles. Reference peak and trough values ​​are obtained based on a continuous cycle signal waveform comprising a predetermined number of cardiac cycles. Normal pressure values ​​in the blood pressure signal sampling waveform are marked based on the reference peak and trough values. Furthermore, the effective value of the intravascular pressure corresponding to a single cycle signal waveform comprising one cardiac cycle is calculated based on the marked normal pressure values ​​in the single cycle signal waveform. In this case, the effective value of the intravascular pressure corresponding to a cardiac cycle is calculated based on the normal pressure values ​​in the cardiac cycle, thereby effectively reducing the adverse effects of signal abnormalities caused by wall adhesion.

[0009] In addition, the signal processing method of the present disclosure optionally further includes determining whether the ratio of the interval between adjacent peaks of the continuous period signal waveform to the cardiac cycle falls within a first interval, and determining whether the ratio of the interval between adjacent valleys of the continuous period signal waveform to the cardiac cycle falls within a second interval. If the ratio of the interval between adjacent peaks of the continuous period signal waveform to the cardiac cycle falls within the first interval and the ratio of the interval between adjacent valleys of the continuous period signal waveform to the cardiac cycle falls within the second interval, then calculating the effective peak value and effective valley value of the continuous period signal waveform. In this way, the effective peak value and effective valley value can be obtained more accurately.

[0010] In addition, in the signal processing method of the present disclosure, 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 reselected. In this case, by determining the fluctuation of the peak value and the fluctuation of the valley value, a continuous periodic signal waveform that is more suitable for calculating the effective peak value and the effective valley value can be selected.

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

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

[0013] Furthermore, in the signal processing method of the present disclosure, optionally, 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 the third threshold, the average of all pressure values ​​marked as normal in the single-cycle signal waveform is used as the effective value of the intravascular pressure corresponding to the single-cycle signal waveform. This allows for more accurate acquisition of the effective value of the intravascular pressure.

[0014] In addition, in the signal processing method involved in the present disclosure, optionally, in the single-cycle 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-cycle signal waveform is marked as valid; 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-cycle signal waveform is marked as invalid.

[0015] In addition, in the signal processing method involved in the present disclosure, optionally, in the single-cycle 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, the effective value of the intravascular pressure corresponding to the single-cycle signal waveform is obtained based on at least one cardiac cycle marked as valid that is closest to the single-cycle signal waveform.

[0016] In addition, in the signal processing method involved in the present disclosure, optionally, the pressure measuring device includes a pressure sensor for acquiring a blood pressure signal and a pushing tool for pushing the pressure sensor.

[0017] In addition, the present disclosure also provides an intravascular pressure measurement system, which uses the signal processing method involved in the present disclosure.

[0018] According to the present disclosure, the adverse effects of abnormal signals caused by wall adhesion during intravascular pressure measurement can be effectively reduced. BRIEF DESCRIPTION OF THE 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 2 is a schematic diagram showing an application of an FFR measurement system according to an example of the present disclosure.

[0021] Figure 2 It is an enlarged schematic diagram showing the proximal pressure measuring device and the distal pressure measuring device involved in the example of the present disclosure being inserted into a blood vessel.

[0022] Figure 3 FIG. 1 is a block diagram illustrating a signal processor according to an example of the present disclosure.

[0023] Figure 4 Schematic diagram showing a blood pressure signal sampling waveform involved in an example of the present disclosure.

[0024] Figure 5 Schematic diagram showing a continuous periodic signal waveform involved in an example of the present disclosure.

[0025] Figure 6A FIG. 1 is a schematic diagram showing a display device according to an example of the present disclosure displaying an unprocessed FFR.

[0026] 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.

[0027] Figure 7A 1 is a schematic diagram showing the overall flow of the signal processing method for FFR measurement involved in the examples of the present disclosure.

[0028] Figure 7B 3 is a schematic diagram showing a process of obtaining a reference peak value and a reference valley value involved in an example of the present disclosure.

[0029] Figure 8 3 is a flow chart showing a signal processing method for measuring intravascular pressure according to an example of the present disclosure. DETAILED DESCRIPTION

[0030] The preferred embodiments of the present disclosure are described in detail below with reference to the accompanying drawings. In the following description, identical components are assigned identical reference numerals, and duplicate descriptions are omitted. In addition, the accompanying drawings are merely schematic, and the proportions of the dimensions of the components and the shapes of the components may differ from the actual ones.

[0031] It should be noted that the terms "including" and "having" and any variations thereof in this disclosure, such as a process, method, system, product or device that includes or has a series of steps or units, are not necessarily limited to those steps or units clearly listed, but may include or have other steps or units that are not clearly listed or are inherent to these processes, methods, products or devices.

[0032] In addition, the subheadings and the like in the following description of this disclosure are not intended to limit the content or scope of this disclosure, but are merely provided as a guide for reading. Such subheadings should not be understood as dividing the content of the article, nor should the content under the subheading be limited to the scope of the subheading.

[0033] Embodiments of the present disclosure provide an intravascular pressure measurement system that can acquire a blood pressure signal at a predetermined location within a blood vessel and process the signal to obtain an effective value of the intravascular pressure at the predetermined location. In various embodiments, the intravascular pressure measurement system may 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 location within a blood vessel to obtain an effective value of the FFR at that location. In various embodiments, the FFR measurement system may also be referred to as a medical measurement system, an FFR monitoring system, or the like. Embodiments of the present disclosure provide a signal processing method for measuring intravascular pressure. This method can process the acquired blood pressure signal at a predetermined location within a blood vessel to obtain an effective value of the intravascular pressure.

[0035] An embodiment of the present disclosure provides a signal processing method for FFR measurement, which can process a blood pressure signal obtained at a predetermined position in a blood vessel to obtain an effective value of FFR.

[0036] Figure 1 2 is a schematic diagram showing an application of the FFR measurement system 1 involved in the example of the present disclosure.

[0037] Figure 2 FIG1 is an enlarged schematic diagram showing the proximal pressure measurement device 10 and the distal pressure measurement device 20 involved in an example of the present disclosure intervening in a blood vessel.

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

[0039] In various embodiments, the FFR measurement system 1 may include a proximal pressure measurement device 10, a distal pressure measurement device 20, and a signal processor 30 (see Figure 1 and Figure 2 The proximal pressure measuring device 10 can obtain the stenosis proximal side S p The distal pressure measuring device 20 can obtain the blood pressure signal of the distal side of the stenosis S d The signal processor 30 can receive and process the blood pressure signal of the stenosis proximal side S p Blood pressure signal and S distal to stenosis d The blood pressure signal is used to obtain the effective value of FFR.

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

[0041] In various embodiments, the proximal pressure measuring device 10 can be connected to the outlet of the coronary artery to measure the blood pressure signal at the outlet of the coronary artery. p To obtain the S proximal side of the stenosis p Blood pressure signal (see Figure 2 For example, the proximal pressure measuring device 10 can be passed through the intervening blood vessel and along the blood vessel from the stenosis proximal side S p The hollow guiding catheter extending outside the body is connected to the proximal side of the stenosis S p .

[0042] In various embodiments, the stenosis proximal side S obtained by the proximal pressure measurement device 10 p The blood pressure signal can be an analog signal. In various embodiments, the stenosis proximal side S obtained by the proximal pressure measuring device 10 pThe blood pressure signal may include pressure information and time information. p The blood pressure signal can be used to obtain the S p The mean pressure, for example, will be S on the proximal side of the stenosis p The blood pressure signal is converted into a digital signal that can be used to represent the pressure value and averaged.

[0043] In various embodiments, based on the stenosis proximal side S p The blood pressure signal can be used to obtain the cardiac cycle. p The blood pressure signal can be a signal in which the pressure information changes periodically with time information. The duration of one cycle of the pressure information changing with time information can be regarded as the duration of one cardiac cycle. In this embodiment, the cardiac cycle generally refers to the time it takes for the heart to contract and relax once. In various embodiments, the proximal side S of the stenosis obtained by the proximal pressure measuring device 10 is p The blood pressure signal may include blood pressure signals of multiple consecutive cardiac cycles.

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

[0045] In various embodiments, the distal pressure measurement device 20 may include a pressure sensor 21 for acquiring a blood pressure signal, and a pushing tool 22 for pushing the pressure sensor 21 (see FIG. Figure 2 The pressure sensor 21 can be introduced into the blood vessel and can measure the pressure in the blood vessel. The pressure sensor 21 can be set on the pushing tool 22, and the pushing tool 22 can be extended 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 place the pressure sensor 21 at a predetermined position in the blood vessel, for example, at the distal side S of the stenosis. d .

[0046] In various embodiments, as described above, the pressure sensor 21 can be introduced into the blood vessel and can measure the pressure 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, at the distal side of the stenosis S d , to obtain the S distal to the stenosis d Blood pressure signal (see Figure 2 ).

[0047] In various embodiments, the pressure sensor 21 can be a pressure sensor for measuring fluid pressure. The pressure sensor 21 can obtain a blood pressure signal by sensing the fluid pressure of 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 a photoelectric pressure sensor. In some examples, the pressure sensor 21 can be a silicon-based pressure sensing device. 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 via a wired method, such as via a signal line (not shown) provided on the pushing tool. In other examples, the blood pressure signal acquired by the pressure sensor 21 can also be transmitted to the outside of the body via a wireless transmission method, such as Bluetooth, WIFI, or NFC.

[0049] In various embodiments, the pressure sensor 21 can measure pressure within the blood vessel at a predetermined sampling frequency. In various embodiments, the pressure sensor 21 can continuously measure pressure within the blood vessel at a predetermined sampling frequency. In some examples, the pressure sensor 21 can measure pressure within the blood vessel at a sampling frequency of 100-500 times / second. For example, 100 times / second, 150 times / second, 200 times / second, 250 times / second, 300 times / second, 400 times / second, or 500 times / second. In other words, the pressure sensor 21 can acquire 100-500 blood pressure signals per second within the blood vessel to represent the intravascular pressure.

[0050] In some examples, the blood pressure signal acquired by the pressure sensor 21 may be an analog signal. In various embodiments, the blood pressure signal acquired by the pressure sensor 21 may include pressure information and time information. In various embodiments, a cardiac cycle may 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 may be a signal in which pressure information changes periodically with time information, and the duration of one cycle of change of pressure information with time information may be considered as the duration of one cardiac cycle. In various embodiments, the blood pressure signal acquired by the pressure sensor 21 may include blood pressure signals of multiple consecutive cardiac cycles.

[0051] In various embodiments, the signal processor 30 may receive and process the blood pressure signal obtained by the pressure sensor 21 to obtain the effective value of the intravascular pressure. In various embodiments, the signal processor 30 may receive and process the stenosis distal side S obtained by the distal pressure measuring device 20. d The blood pressure signal is used to obtain the distal side of the stenosis S dIn various embodiments, the signal processor 30 may also receive and process the stenosis proximal side S p The blood pressure signal is used to obtain the S p In various embodiments, the signal processor 30 may be based on the stenosis distal side S d The effective value of blood pressure and S on the proximal side of stenosis p The effective value of FFR is obtained by measuring the average pressure.

[0052] Figure 3 is a block diagram illustrating a signal processor 30 according to an example of the present disclosure. In various embodiments, the signal processor 30 may include a communication module 31 (see Figure 3 The communication module 31 can communicate with the pressure sensor 21 to receive the blood pressure signal acquired by the pressure sensor 21, such as the blood pressure signal of the distal side of the stenosis S d blood pressure signal.

[0053] In some examples, the communication module 31 may be a wired communication module such as a USB interface, an HDMI interface, or an RS232 interface, and the blood pressure signal acquired by the pressure sensor 21 may be transmitted to the signal processor 30 via a signal line provided on the pushing tool and the communication module 31. In other examples, the communication module 31 may be a wireless communication module such as Bluetooth, WIFI, or NFC, and the blood pressure signal acquired by the pressure sensor 21 may be transmitted to the signal processor 30 wirelessly.

[0054] In various embodiments, the signal processor 30 may further include an analog-to-digital conversion module 32 (see Figure 3 The analog-to-data conversion unit 32 can convert the blood pressure signal (eg, the blood pressure signal on the distal side of the stenosis) acquired by the pressure sensor 21 into d The blood pressure signal) is converted from an analog signal to a digital signal that can be used to represent the pressure value.

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

[0056] In some examples, the signal processor 30 may further include a waveform shaping module 33 (see Figure 3 The waveform shaping module 33 can shape the blood pressure signal including a plurality of consecutive cardiac cycles acquired by the pressure sensor 21 into a blood pressure signal sampling waveform in which the intravascular pressure changes with time. Specifically, since the blood pressure signal acquired by the pressure sensor 21 includes 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 mark the blood pressure signals acquired by the pressure sensor 21 one by one in the coordinate system (for example, the distal side S of the stenosis dThe coordinate points corresponding to the blood pressure signal of the heartbeat are formed to form a blood pressure signal sampling waveform including the pressure changes over time for multiple cardiac cycles (see Figure 4 ).

[0057] In some examples, the signal processor 30 may further include a reference acquisition module 34. The reference acquisition module 34 may acquire a reference peak value and a reference valley value based on the blood pressure signal sampling waveform.

[0058] The benchmark acquisition module 34 acquires the benchmark peak value and the benchmark valley value, which may 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, then calculating the effective peak value and the effective valley value of the continuous cycle signal waveform; and obtaining the benchmark peak value and the benchmark valley value based on the effective peak value and the effective valley value.

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

[0060] In some examples, the benchmark acquisition module 34 acquiring the benchmark peak and benchmark valley may also include: determining whether the ratio of the interval between adjacent peaks of the continuous periodic signal waveform to the cardiac cycle falls within a first interval, for example, 0.8-1.2; determining whether the ratio of the interval between adjacent valleys of the continuous periodic signal waveform to the cardiac cycle falls within a second interval, for example, 0.8-1.2; if the ratio of the interval between any adjacent peaks of the continuous periodic signal waveform to the cardiac cycle falls within the first interval and the ratio of the interval between any adjacent valleys of the continuous periodic signal waveform to the cardiac cycle falls within the second interval, then calculating the effective peak and effective valley of the continuous periodic signal waveform; if the ratio of the interval between any adjacent peaks of the continuous periodic signal waveform to the cardiac cycle does not fall within the first interval or the ratio of the interval between any adjacent valleys of the continuous periodic signal waveform to the cardiac cycle does not fall within the second interval, then reselecting a continuous periodic signal waveform including a predetermined number of cardiac cycles.

[0061] Figure 5 Schematic diagram showing a continuous periodic signal waveform involved in an example of the present disclosure.

[0062] In various embodiments, a continuous cycle signal waveform including a predetermined number of cardiac cycles can be defined as a signal waveform corresponding to a continuous period of time in the blood pressure signal sampling waveform, where the continuous period of time can include a 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 the signal waveform corresponding to the current cardiac cycle in the blood pressure signal sampling waveform. The single-cycle signal waveform can be the signal waveform between one trough and the next trough in the blood pressure signal sampling waveform. In some examples, the third threshold value can be between 0.70 and 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, 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 of the current cardiac cycle is not less than a third threshold, 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 effective value of the intravascular pressure in 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) single-cycle signal waveform marked as valid before and closest to the current cardiac cycle can also be used as the effective value of the intravascular pressure in the current cardiac cycle (e.g., S distal to the stenosis). d In other examples, the effective value of the current cardiac cycle may be obtained based on the average of all pressure values ​​marked as normal in the single-cycle signal waveform of the current cardiac cycle, and 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) marked as effective and located before and closest to the current cardiac cycle, for example, by averaging them.

[0077] In some examples, 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 of the current cardiac cycle is less than a third threshold, 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 cardiac cycle (e.g., 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 11, or 12) marked as valid that is located before the current cardiac cycle and closest to the current cardiac cycle is used as the valid value of the intravascular pressure in the current cardiac cycle (e.g., S distal to the stenosis). 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 the 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] FIG6 is a schematic diagram showing a display device according to an example of the present disclosure showing FFR. 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.

[0081] 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 ).

[0082] 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 stenosis distal side Sd The first display area 41 and the second display area 42 may be used to display a blood pressure signal, for example, a sampled waveform of a blood pressure signal showing changes in intravascular pressure over time over multiple cardiac cycles. The second display area 42 may be used to display the FFR value. In some examples, the first display area 41 and the second display area 42 may share the same horizontal axis (i.e., the time axis).

[0083] In some examples, if there is a pressure value marked as abnormal in the blood pressure signal sampling waveform, the first display area 41 can display the uncorrected waveform, and the second display area 42 can display the unprocessed FFR value (see Figure 6A ).

[0084] In some examples, if there is a pressure value marked as abnormal in the blood pressure signal sampling waveform, the first display area 41 can display the uncorrected waveform, and the second display area can display the effective value of FFR (see Figure 6B In this case, it can not only help the doctor to know the effective value of FFR, but also facilitate the doctor to find out the adhesion condition of the distal pressure measuring device 20 to the wall.

[0085] In other examples, if there is a pressure value marked as abnormal in the blood pressure signal sampling waveform, the first display area 41 can correct the waveform of the cardiac cycle based on the effective value of the intravascular pressure corresponding to each cardiac cycle and display the corrected waveform, and the second display area 42 can display the effective value of FFR.

[0086] In various embodiments, the FFR measurement system 1 may also not include the proximal pressure measurement device 10, thereby providing a pressure measurement system for measuring pressure within a blood vessel. In various embodiments, the pressure measurement system may include the distal pressure measurement device 20 and the signal processor 30 of the present disclosure. The distal pressure measurement device 20 can be introduced into a blood vessel and can obtain a blood pressure signal at a predetermined location within the vessel. The signal processor 30 can process the blood pressure signal obtained by the distal pressure measurement device 20 to obtain an effective value of the intravascular pressure at the predetermined location. In various embodiments, the pressure measurement system may also include the display device 40 of the present disclosure, which can display the effective value of the intravascular pressure.

[0087] In various embodiments, the FFR measurement system 1 may also not include the proximal pressure measuring device 10 and the distal pressure measuring device 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 may process the blood pressure signal in the blood vessel obtained by other devices to obtain the effective value of the intravascular pressure. In various embodiments, the signal processing system may process the blood pressure signal in the blood vessel obtained by other devices to obtain the effective value of FFR. In various embodiments, the signal processing system may include the signal processor 30 involved in the present disclosure, and process the blood pressure signal in the blood vessel obtained by other devices through the signal processor 30. In various embodiments, the signal processing system may 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 FFR through the display device 40.

[0088] FIG7 is a flow chart showing a signal processing method for FFR measurement according to an example of the present disclosure. Figure 7A is a schematic diagram showing the overall flow of the signal processing method for FFR measurement involved in the example of the present disclosure, Figure 7B This is a schematic diagram showing the process of obtaining the reference peak value and the reference valley value involved in the example of the present disclosure. Figure 7A and Figure 7B , details the signal processing method for FFR measurement involved in the examples of this disclosure.

[0089] Various embodiments of the present disclosure provide a signal processing method for FFR measurement (see Figure 7A ), which may include: obtaining the stenosis proximal side S p Blood pressure signal and S distal to stenosis d Blood pressure signal; S d The blood pressure signal is waveform-shaped to obtain a blood pressure signal sampling waveform including a plurality of cardiac cycles in which the intravascular pressure changes with time; based on the blood pressure signal sampling waveform, a reference peak value and a reference valley value are obtained; based on the reference peak value and the reference valley value, a normal pressure value in the blood pressure signal sampling waveform is identified and marked; based on the pressure value marked as normal in a single-cycle signal waveform including one cardiac cycle, the distal side S of the stenosis corresponding to the cardiac cycle is obtained. d Effective value of blood pressure; based on the proximal side of the stenosis S p The blood pressure signal of the distal side of the stenosis within one cardiac cycle S d The effective value of blood pressure is used to obtain the effective value of FFR in the corresponding cardiac cycle.

[0090] In the signal processing method for FFR measurement according to the example of the present disclosure, the stenosis proximal side S is obtained. p Blood pressure signal and S distal to stenosisd In some examples, the blood pressure signal of the stenosis proximal side S p The blood pressure signal can be obtained by the proximal pressure measurement device 10 of the present disclosure. d The blood pressure signal can be obtained by the distal pressure measurement device 20 involved in the present disclosure. p The blood pressure signal can be used to obtain the cardiac cycle.

[0091] In the signal processing method for FFR measurement according to the example of the present disclosure, the distal side S of the stenosis is d The blood pressure signal is subjected to waveform shaping to obtain a blood pressure signal sampling waveform including a plurality of cardiac cycles in which the intravascular pressure changes with time. In various embodiments, it may include: receiving the stenosis distal side S d Blood pressure signal; S d The blood pressure signal is converted from an analog signal to a digital signal that can be used to represent the pressure value; the horizontal axis represents time and the vertical axis represents pressure, and the distal side of the stenosis S is marked one by one in the coordinate system. d The coordinate point corresponding to the blood pressure signal; in the coordinate system, a blood pressure signal sampling waveform including the pressure changes over time for multiple cardiac cycles is formed (see Figure 4 In various embodiments, the stenosis distal side S can be converted to d The blood pressure signal is converted from an analog signal to a digital signal that can be used to represent the pressure value. In various embodiments, the waveform shaping module 33 involved in the examples of the present disclosure can form a blood pressure signal sampling waveform including pressure changes over time for multiple cardiac cycles.

[0092] In the signal processing method for FFR measurement involved in the example 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 may include: selecting a continuous periodic 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 periodic signal waveform is not greater than a first threshold value; judging whether the fluctuation of the valley value of the continuous periodic signal waveform is not greater than a second threshold value; 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, obtaining the effective peak value and the effective valley value of the continuous periodic 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 peak value and the reference valley value may be obtained by the reference acquisition module 34 involved in the examples of the present disclosure.

[0093] In the signal processing method for FFR measurement involved in the examples of the present disclosure, 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. In various embodiments, it 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; 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. In some examples, if the pressure value does not fall within the range of the reference peak value and the reference valley value, the pressure value is marked as abnormal. In various embodiments, the normal pressure value in the blood pressure signal sampling waveform can be identified and marked by the normal identification module 35 involved in the examples of the present disclosure.

[0094] In the signal processing method for FFR measurement involved in the example of the present disclosure, 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), the effective value of the intravascular pressure corresponding to the cardiac cycle (for example, S on the distal side of the stenosis) is obtained. d Effective value of blood pressure). In various embodiments, it may include: 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, 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. In various embodiments, the effective value of the intravascular pressure corresponding to the current cardiac cycle (for example, the effective value of the distal side S of the stenosis) can be obtained by the blood pressure effective value acquisition module 36 involved in the examples of the present disclosure. d effective value of blood pressure).

[0095] In the signal processing method for FFR measurement according to the example of the present disclosure, based on the stenosis proximal side S p The blood pressure signal of the distal side of the stenosis S d The effective value of blood pressure is used to obtain the effective value of FFR in the current cardiac cycle. In various embodiments, it may include: based on the proximal side S of the stenosis 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 the S p In various embodiments, the effective value of FFR in the current cardiac cycle can be obtained by the FFR effective value acquisition module 37 involved in the examples of the present disclosure.

[0096] Figure 8 1 is a flow chart showing a signal processing method for measuring intravascular pressure according to an example of the present disclosure. Figure 8 , a detailed description of the signal processing method for measuring intravascular pressure involved in the example of the present disclosure is given.

[0097] Various embodiments of the present disclosure provide a signal processing method for measuring intravascular pressure (see Figure 8 ), which may include: obtaining a blood pressure signal at a predetermined position in a blood vessel; waveform shaping the blood pressure signal at the predetermined position to obtain a blood pressure signal sampling waveform including changes in the intravascular pressure over time for multiple cardiac cycles; obtaining 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; obtaining an effective value of the intravascular pressure corresponding to the cardiac cycle based on the pressure value marked as normal in a single-cycle signal waveform including one cardiac cycle.

[0098] In the signal processing method for measuring intravascular pressure according to the examples of the present disclosure, a blood pressure signal is obtained at a predetermined location within the blood vessel. In some examples, the blood pressure signal at the predetermined location can be obtained using the distal pressure measurement device 20 according to the examples of the present disclosure. In various embodiments, the cardiac cycle can be obtained based on the blood pressure signal at the predetermined location.

[0099] In the signal processing method for measuring intravascular pressure involved in the example of the present disclosure, the blood pressure signal at a predetermined position is waveform-shaped to obtain a blood pressure signal sampling waveform including the changes in intravascular pressure over time for multiple cardiac cycles. In various embodiments, it may include: receiving the blood pressure signal at the predetermined position; converting the blood pressure signal at the predetermined position from an analog signal to a digital signal that can be used to represent the pressure value; using the horizontal axis to represent time and the vertical axis to represent pressure, marking the coordinate points corresponding to the blood pressure signal at the predetermined position in the coordinate system one by one; forming a blood pressure signal sampling waveform including the changes in pressure over time for multiple cardiac cycles in the coordinate system (see Figure 4 In various embodiments, the analog-to-digital conversion module 32 of the present disclosure can convert the blood pressure signal at a predetermined location from an analog signal into a digital signal that can be used to represent the pressure value. In various embodiments, the waveform shaping module 33 of the present disclosure can form a blood pressure signal sampling waveform that includes pressure changes over time for multiple cardiac cycles.

[0100] In the signal processing method for measuring intravascular pressure involved in the examples of the present disclosure, a reference peak value and a reference valley value are obtained based on the blood pressure signal sampling waveform. In various embodiments, this may include: selecting a continuous cycle signal waveform including a predetermined number of cardiac cycles from the blood pressure signal sampling waveform; determining whether the fluctuation of the peak value of the continuous cycle signal waveform is not greater than a first threshold; determining whether the fluctuation of the valley value of the continuous cycle signal waveform is not greater than a second threshold; if the fluctuation of the peak value of the continuous cycle signal waveform is not greater than the first threshold and the fluctuation of the valley value of the continuous cycle signal waveform is not greater than the second threshold, then calculating the effective peak value and the effective valley value of the continuous cycle 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 peak value and the reference valley value can be obtained by the reference acquisition module 34 involved in the examples of the present disclosure.

[0101] In the signal processing method for measuring intravascular pressure involved in the examples of the present disclosure, 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. In various embodiments, it 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; 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, the pressure value is marked as abnormal. In various embodiments, the normal pressure value in the blood pressure signal sampling waveform can be identified and marked by the normal identification module 35 involved in the examples of the present disclosure.

[0102] In the signal processing method for measuring intravascular pressure involved in the example of the present disclosure, based on the pressure value marked as normal in a single-cycle signal waveform including one cardiac cycle (hereinafter, the current cardiac cycle is taken as an example for explanation), the effective value of the intravascular pressure corresponding to the cardiac cycle is obtained. In various embodiments, it may include: 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. In various embodiments, the effective value of the intravascular pressure corresponding to the current cardiac cycle can be obtained by the blood pressure effective value acquisition module 36 involved in the example of the present disclosure.

[0103] According to the present disclosure, the adverse effects of abnormal signals caused by wall adhesion during intravascular pressure measurement can be effectively reduced.

[0104] Although the present disclosure has been described in detail above with reference to the accompanying drawings and examples, it will be understood that the above description does not limit the present disclosure in any form. Those skilled in the art may modify and change the present disclosure as needed without departing from the spirit and scope of the present disclosure, and such modifications and variations all fall within the scope of the present disclosure.

Claims

1. A reference acquisition method for identifying normal pressure values, characterized in that: include: Acquiring a blood pressure signal sampling waveform including a variation of intravascular pressure over time during a plurality of cardiac cycles, wherein the blood pressure signal sampling waveform is measured by a pressure measuring device at a predetermined position within the blood vessel; Selecting a continuous cycle signal waveform including a predetermined number of cardiac cycles from the blood pressure signal sampling waveform; Determine whether the fluctuation of the peak value of the continuous periodic signal waveform is no greater than a first threshold value, and determine whether the fluctuation of the valley value of the continuous periodic signal waveform is no greater than a second threshold value, if the fluctuation of the peak value of the continuous periodic signal waveform is no greater than the first threshold value and the fluctuation of the valley value of the continuous periodic signal waveform is no greater than the second threshold value, then calculate the effective peak value and effective valley value of the continuous periodic signal waveform, or if the ratio of the interval between any adjacent peak values ​​of the continuous periodic signal waveform and the cardiac cycle falls within a first interval and the ratio of the interval between any adjacent valley values ​​of the continuous periodic signal waveform and the cardiac cycle falls within a second interval, then calculate the effective peak value and effective valley value of the continuous periodic signal waveform, wherein the effective peak value is the average value or median value of the peak value of the continuous periodic signal waveform, and the effective valley value is the average value or median value of the valley value of the continuous periodic signal waveform; and A reference peak value and a reference valley value are obtained based on the effective peak value and the effective valley value. The reference peak value and the reference valley value are used to identify a normal pressure value in the blood pressure signal sampling waveform. 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, and f2 represents the second factor.

2. The benchmark acquisition method according to claim 1, characterized in that: In the identification, 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; otherwise, the pressure value is marked as abnormal.

3. The benchmark acquisition method according to claim 1, characterized in that: If the fluctuation of the peak value of the continuous periodic signal waveform is greater than the first threshold or the fluctuation of the valley value of the continuous periodic signal waveform is greater than the second threshold, the continuous periodic signal waveform is reselected.

4. The benchmark acquisition method according to claim 1, wherein: If the ratio of the interval between any adjacent peak values ​​of the continuous periodic signal waveform to the cardiac cycle does not fall within the first interval or the ratio of the interval between any adjacent valley values ​​of the continuous periodic signal waveform to the cardiac cycle does not fall within the second interval, a continuous periodic signal waveform including the predetermined number of cardiac cycles is reselected.

5. The benchmark acquisition method according to claim 1, characterized in that: The first factor is 0.05 to 0.30, and the second factor is 0.05 to 0.

30.

6. The benchmark acquisition method according to claim 1, characterized in that: The blood pressure signal acquired by the pressure measuring device is an analog signal, and the blood pressure signal sampling waveform is obtained by converting the blood pressure signal from the analog signal into a digital signal representing the pressure value and performing waveform shaping on the digital signal.

7. A benchmark acquisition module, characterized in that: The benchmark acquisition module is configured to: Acquiring a blood pressure signal sampling waveform including a variation of intravascular pressure over time for a plurality of cardiac cycles, wherein the blood pressure signal sampling waveform is obtained by measuring pressure at a predetermined location within the blood vessel using a pressure measuring device at a predetermined sampling frequency; Selecting a continuous cycle signal waveform including a predetermined number of cardiac cycles from the blood pressure signal sampling waveform; determining whether the fluctuation of the peak value of the continuous periodic signal waveform is no greater than a first threshold value, and determining whether the fluctuation of the valley value of the continuous periodic signal waveform is no greater than a second threshold value, if the fluctuation of the peak value of the continuous periodic signal waveform is no greater than the first threshold value and the fluctuation of the valley value of the continuous periodic signal waveform is no greater than the second threshold value, calculating the effective peak value and the effective valley value of the continuous periodic signal waveform, or if the ratio of the interval between any adjacent peak values ​​of the continuous periodic signal waveform to the cardiac cycle falls within a first interval and the ratio of the interval between any adjacent valley values ​​of the continuous periodic signal waveform to the cardiac cycle falls within a second interval, calculating the effective peak value and the effective valley value of the continuous periodic signal waveform; and A reference peak value and a reference valley value are obtained based on the effective peak value and the effective valley value. The reference peak value and the reference valley value are used to identify a normal pressure value in the blood pressure signal sampling waveform. 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, and f2 represents the second factor.

Images