CN112494016B

CN112494016B - Host for processing pressure signals

Info

Publication number: CN112494016B
Application number: CN201911416527.1A
Authority: CN
Inventors: 李连波; 郑欲晓
Original assignee: Insight Lifetech Co Ltd
Current assignee: Insight Lifetech Co Ltd
Priority date: 2019-12-31
Filing date: 2019-12-31
Publication date: 2024-02-02
Anticipated expiration: 2039-12-31
Also published as: CN112494016A

Abstract

The present disclosure relates to a method of tracking cardiac circulatory events using blood pressure, comprising: and simultaneously measuring the pressure near the proximal end side in the blood vessel and the pressure far from the proximal end side in the blood vessel for a plurality of times in any cardiac cycle, generating a first initial pressure signal and a second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio, sequentially selecting a preset number of pressure ratios from the initial pressure ratios in order from small to large, and calculating the average value of the preset number of pressure ratios according to the selected preset number of pressure ratios.

Description

Host for processing pressure signals

Technical Field

The present disclosure relates specifically to a host for processing pressure signals.

Background

Coronary artery disease is one of the leading causes of death worldwide, and the ability to better diagnose, monitor and treat coronary artery disease can save lives. Coronary angiography is a technique conventionally used to evaluate stenotic lesions of coronary arteries, but it does not reflect the reality of coronary vascular function, so it is basically unclear whether or not a stenotic lesion coronary artery is associated with myocardial ischemia, symptoms of a patient. Currently, a method for clinically judging stenosis of coronary arteries mainly uses a blood flow reserve fraction (Fractional Flow Reserve, abbreviated as FFR) technique obtained by pressure guide wire examination.

However, the following drawbacks exist in obtaining FFR: the need to inject a hyperemic evoked drug (e.g., adenosine triphosphate ATP) into the coronary arteries prior to FFR measurement, to place the coronary arteries in a maximal hyperemic state, increases clinical procedure time, adds significant medical costs while providing patient with an off-indication, and also causes the patient to develop an allergic response.

Disclosure of Invention

The present disclosure has been made in view of the above-described circumstances, and an object thereof is to provide a method capable of tracking cardiac circulatory events using blood pressure more safely and effectively without the need for injection of a congestion-inducing drug.

To this end, a first aspect of the present disclosure provides a method for tracking cardiac circulatory events using blood pressure, comprising: measuring the side pressure close to the proximal end in the blood vessel at a certain sampling rate in any one cardiac cycle and generating a first initial pressure signal, and measuring the side pressure far from the proximal end in the blood vessel at a certain sampling rate and generating a second initial pressure signal; according to the first initial pressure signal and the second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio, sequentially selecting a preset number of pressure ratios from the initial pressure ratios in order from small to large, and calculating the average value of the preset number of pressure ratios according to the selected preset number of pressure ratios.

In the present disclosure, the pressure in the blood vessel near the proximal side and the pressure in the blood vessel far from the proximal side are measured simultaneously and a first initial pressure signal and a second initial pressure signal are generated multiple times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. And sequentially selecting a preset number of pressure ratios from the initial pressure ratios in a descending order, and calculating the average value of the preset number of pressure ratios according to the selected preset number of pressure ratios. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

In the intravascular pressure measurement system according to the first aspect of the present disclosure, optionally, the cardiac cycle includes a full cycle of diastole and systole. Thereby, the blood vessel pressure in the diastole and systole phases can be obtained.

A second aspect of the present disclosure provides a method for tracking cardiac circulatory events using blood pressure, comprising: measuring the intravascular proximal side pressure at a sampling rate and generating a first initial pressure signal and the intravascular distal side pressure at a sampling rate and generating a second initial pressure signal during any one cardiac cycle, the cardiac cycle including diastole and systole of diastole; according to the first initial pressure signal and the second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio, obtaining the pressure ratio in the diastole of the cardiac cycle from the initial pressure ratio, and selecting the minimum pressure ratio from the pressure ratio values.

In the present disclosure, the pressure in the blood vessel near the proximal side and the pressure in the blood vessel far from the proximal side are measured simultaneously and a first initial pressure signal and a second initial pressure signal are generated multiple times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. The pressure ratio value within the diastole of the cardiac cycle is obtained from the initial pressure ratio value and the minimum pressure ratio value is selected from the pressure ratio values. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

A third aspect of the present disclosure provides a method of tracking cardiac circulatory events using blood pressure, comprising: measuring the side pressure close to the proximal end in the blood vessel at a certain sampling rate in any one cardiac cycle and generating a first initial pressure signal, and measuring the side pressure far from the proximal end in the blood vessel at a certain sampling rate and generating a second initial pressure signal; calculating a ratio of a pressure value of the second initial pressure signal to a pressure value of the first initial pressure signal corresponding to a pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio, obtaining a pressure ratio in a first preset period of the cardiac cycle from the initial pressure ratios, and selecting a minimum pressure ratio from the pressure ratio values, wherein a mean value of the pressure values of the first initial pressure signal is obtained according to the first initial pressure signal, a first intersection point is obtained according to the first initial pressure signal and the mean value, and the first preset period is a period from the first intersection point to the minimum value of the first initial pressure signal and the first initial pressure signal is continuously reduced.

In the present disclosure, the pressure in the blood vessel near the proximal side and the pressure in the blood vessel far from the proximal side are measured simultaneously and a first initial pressure signal and a second initial pressure signal are generated multiple times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. The pressure ratio value is obtained from the initial pressure ratio value for a first predetermined period of the cardiac cycle, and a minimum pressure ratio value is selected from the pressure ratio values. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

A fourth aspect of the present disclosure provides a method for tracking cardiac circulatory events using blood pressure, comprising: measuring the side pressure close to the proximal end in the blood vessel at a certain sampling rate in any one cardiac cycle and generating a first initial pressure signal, and measuring the side pressure far from the proximal end in the blood vessel at a certain sampling rate and generating a second initial pressure signal; according to the first initial pressure signal and the second initial pressure signal, calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal to obtain an initial pressure ratio value, obtaining the pressure ratio value in a second preset period of the cardiac cycle from the initial pressure ratio values, and selecting the pressure ratio value corresponding to the midpoint time of the second preset period from the pressure ratio values, wherein the average value of the pressure values of the first initial pressure signal is obtained according to the first initial pressure signal, the first intersection point is obtained according to the first initial pressure signal and the average value, and the second preset period is the period from the first intersection point to the minimum value of the first initial pressure signal.

In the present disclosure, the pressure in the blood vessel near the proximal side and the pressure in the blood vessel far from the proximal side are measured simultaneously and a first initial pressure signal and a second initial pressure signal are generated multiple times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. And obtaining a pressure ratio value in a second preset period of the cardiac cycle from the initial pressure ratio value, and selecting a pressure ratio value corresponding to the midpoint time of the second preset period from the pressure ratio value. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

A fifth aspect of the present disclosure provides a method for tracking cardiac circulatory events using blood pressure, comprising: measuring the side pressure close to the proximal end in the blood vessel at a certain sampling rate in any one cardiac cycle and generating a first initial pressure signal, and measuring the side pressure far from the proximal end in the blood vessel at a certain sampling rate and generating a second initial pressure signal; calculating a ratio of a pressure value of the second initial pressure signal to a pressure value of the first initial pressure signal corresponding to a pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio, obtaining a pressure ratio in a third preset period of the cardiac cycle from the initial pressure ratio, and calculating an average value of the pressure ratios, wherein an average value of the pressure values of the first initial pressure signal is obtained according to the first initial pressure signal, a first intersection point is obtained according to the first initial pressure signal and the average value, and the third preset period is a period from the first intersection point to 80% of the cardiac cycle.

In the present disclosure, the pressure in the blood vessel near the proximal side and the pressure in the blood vessel far from the proximal side are measured simultaneously and a first initial pressure signal and a second initial pressure signal are generated multiple times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. The pressure ratio is obtained from the initial pressure ratio over a third preset period of the cardiac cycle and an average of the pressure ratios is calculated. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

A sixth aspect of the present disclosure provides a method for tracking cardiac circulatory events using blood pressure, comprising: measuring the side pressure close to the proximal end in the blood vessel at a certain sampling rate in any one cardiac cycle and generating a first initial pressure signal, and measuring the side pressure far from the proximal end in the blood vessel at a certain sampling rate and generating a second initial pressure signal; calculating a ratio of a pressure value of the second initial pressure signal to a pressure value of the first initial pressure signal corresponding to a pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio, obtaining a pressure ratio in a second preset period of the cardiac cycle from the initial pressure ratio, and calculating an average value of the pressure ratios, wherein an average value of the pressure values of the first initial pressure signal is obtained according to the first initial pressure signal, a first intersection point is obtained according to the first initial pressure signal and the average value, and the second preset period is a period from the first intersection point to a minimum value of the first initial pressure signal.

In the present disclosure, the pressure in the blood vessel near the proximal side and the pressure in the blood vessel far from the proximal side are measured simultaneously and a first initial pressure signal and a second initial pressure signal are generated multiple times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. The pressure ratio is obtained from the initial pressure ratio over a second preset period of the cardiac cycle and an average of the pressure ratios is calculated. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

A seventh aspect of the present disclosure provides a method for tracking cardiac circulatory events using blood pressure, comprising: measuring the side pressure close to the proximal end in the blood vessel at a certain sampling rate in any one cardiac cycle and generating a first initial pressure signal, and measuring the side pressure far from the proximal end in the blood vessel at a certain sampling rate and generating a second initial pressure signal; calculating a ratio of a pressure value of the second initial pressure signal to a pressure value of the first initial pressure signal corresponding to a pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal, obtaining an initial pressure ratio value, obtaining a pressure ratio value in a fourth preset period of the cardiac cycle from the initial pressure ratio values, and selecting a pressure ratio value corresponding to a midpoint time of the fourth preset period from the pressure ratio values, wherein a derivative of the second initial pressure signal with respect to time is obtained according to the second initial pressure signal, and a first midpoint time and a second midpoint time are obtained according to the second initial pressure signal and the derivative, and the fourth preset period is a period from the first midpoint time to the second midpoint time.

In the present disclosure, the pressure in the blood vessel near the proximal side and the pressure in the blood vessel far from the proximal side are measured simultaneously and a first initial pressure signal and a second initial pressure signal are generated multiple times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. And obtaining the pressure ratio in the fourth preset period of the cardiac cycle from the initial pressure ratio, and selecting the pressure ratio corresponding to the midpoint time of the fourth preset period from the pressure ratio values. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

An eighth aspect of the present disclosure provides a method for tracking cardiac circulatory events using blood pressure, comprising: measuring the side pressure close to the proximal end in the blood vessel at a certain sampling rate in any one cardiac cycle and generating a first initial pressure signal, and measuring the side pressure far from the proximal end in the blood vessel at a certain sampling rate and generating a second initial pressure signal; calculating a ratio of a pressure value of the second initial pressure signal to a pressure value of the first initial pressure signal corresponding to a pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal, obtaining an initial pressure ratio value, obtaining a pressure ratio value in a fifth preset period of the cardiac cycle from the initial pressure ratio value, and calculating an average value of the pressure ratio values, wherein the fifth preset period is a target derivative value with the largest occurrence number of the derivative value of the second pressure signal relative to time in the fourth preset period and is a period from the first occurrence to the last occurrence of the target derivative value in the fourth preset period, obtaining a derivative of the second initial pressure signal relative to time according to the second initial pressure signal, obtaining a first midpoint time and a second midpoint time according to the second initial pressure signal and the derivative, and obtaining a fourth preset period from the first midpoint time to the second midpoint time.

In the present disclosure, the pressure in the blood vessel near the proximal side and the pressure in the blood vessel far from the proximal side are measured simultaneously and a first initial pressure signal and a second initial pressure signal are generated multiple times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. The pressure ratio is obtained from the initial pressure ratio over a fifth preset period of the cardiac cycle and an average of the pressure ratios is calculated. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

According to the present invention, a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion-inducing drug and that is safer and more effective can be provided.

Drawings

Fig. 1 is a schematic diagram showing the structure of an intravascular pressure measurement system according to an example of the present disclosure.

Fig. 2 is a schematic diagram illustrating an intravascular pressure measurement system according to an example of the present disclosure.

Fig. 3 is a schematic diagram illustrating an interventional human body of an intravascular pressure measurement system according to an example of the present disclosure.

Fig. 4 is a cross-sectional view illustrating an application of an intravascular pressure measurement system according to an example of the present disclosure to a coronary artery.

Fig. 5 is a pressure waveform diagram illustrating a plurality of cardiac cycles to which examples of the present disclosure relate.

Fig. 6 is a pressure waveform diagram illustrating one cardiac cycle of fig. 5 in relation to an example of the present disclosure.

Fig. 7 is a pressure waveform diagram illustrating one cardiac cycle of fig. 5 in accordance with another example of the present disclosure.

Reference numerals illustrate:

1 … system, 10 … blood pressure measuring device, 20 … withdrawal device, 30 … host computer, 100 … guide catheter, 100a … proximal side, 100b … distal side, 101 … internal cavity, 102 … first pressure sensor, 110 … blood pressure measuring catheter, 110a … proximal side, 110b … distal side, 111 … internal cavity, 112 … second pressure sensor, 113 … signal path, 201 … drive module, 202 … switch module, 203 … signal receiving module, 300 … image processing device, 310 … blood pressure processing device, 400 … coronary artery, 401 … proximal coronary artery, 402 … distal coronary artery, 403 … stenotic lesion.

Detailed Description

Hereinafter, preferred embodiments of the present disclosure will be described in detail with reference to the accompanying drawings. In the following description, the same members are denoted by the same reference numerals, and overlapping description thereof is omitted. In addition, the drawings are schematic, and the ratio of the sizes of the components to each other, the shapes of the components, and the like may be different from actual ones.

In addition, headings and the like referred to in the following description of the disclosure are not intended to limit the disclosure or scope thereof, but rather are merely indicative of reading. Such subtitles are not to be understood as being used for segmenting the content of the article, nor should the content under the subtitle be limited only to the scope of the subtitle.

The present disclosure provides a method of using blood pressure to track cardiac circulatory events, in which blood pressure can be used more safely and effectively without the need for injection of a congestion-inducing drug, e.g., a lesion in a patient's blood vessel can be determined without the need for injection of a congestion-inducing drug.

Fig. 1 is a schematic diagram showing the structure of an intravascular pressure measurement system 1 according to an example of the present disclosure. Fig. 2 is a schematic diagram showing an intravascular pressure measurement system 1 according to an example of the present disclosure. Fig. 3 is a schematic diagram showing an interventional human body of the intravascular pressure measurement system 1 according to an example of the present disclosure. Fig. 4 is a cross-sectional view showing an application of the intravascular pressure measurement system 1 according to the example of the present disclosure to a coronary artery 400.

In some examples, as shown in fig. 1-3, an intravascular pressure measurement system 1 (simply "system 1") may include a blood pressure measurement device 10, a retraction device 20, and a host 30. The blood pressure measuring device 10 may be coupled to the withdrawal device 20, and the withdrawal device 20 may be coupled to the host computer 30. The blood pressure measuring device 10 may measure intravascular blood pressure (also referred to as "intravascular pressure," simply "blood pressure" and "pressure") and transmit it to the retraction device 20. The retraction device 20 may receive signals (also referred to as "pressure signals") from the blood pressure measurement device 10 including intravascular blood pressure from the blood vessel, and may then transmit the pressure signals to the host computer 30 for processing.

In some examples, as shown in fig. 1 and 2, a side closer to the host 30 (described later) may be a proximal side 30a and a side farther from the host 30 may be a distal side 30b.

The intravascular pressure measurement system 1 according to the present disclosure can measure intravascular blood pressure (also referred to as "intravascular pressure") using interventional catheter techniques to determine a condition of a patient's blood vessel, such as a stenosis 403 (see fig. 4). The intravascular pressure measurement system 1 may be used to measure and process the intravascular pressure of a patient (e.g., to obtain a first target ratio and/or a second target ratio described later), determine the condition of a patient's vascular lesion without the need for injection of a congestion inducing drug, and more specifically determine the size of a stent site to be implanted.

In some examples, a method of using blood pressure to track a cardiac circulatory event may include measuring an intravascular proximal side 30a pressure and generating a first initial pressure signal at a sampling rate and measuring an intravascular distal side 30b pressure and generating a second initial pressure signal (described in detail below) at a sampling rate during any one cardiac cycle.

In some examples, the cardiac cycle may include the entire cycle of diastole, which is diastole, and systole, which is systole. Thereby, the blood vessel pressure in the diastole and systole phases can be obtained.

In some examples, the blood pressure measurement device 10 may measure the pressure within the blood vessel near the proximal side 30a and generate a pressure signal, and the blood pressure measurement device 10 may measure the pressure within the blood vessel far from the proximal side 30a and generate a pressure signal. For example, the blood pressure measurement device 10 may include a proximal pressure measurement device (described later) that may be used to measure the pressure within the blood vessel near the proximal side 30a and generate a pressure signal. The blood pressure measuring device 10 may include a distal pressure measuring device (described later) that may be used to measure the pressure within the blood vessel near the proximal side 30a and generate a pressure signal.

In some examples, as shown in fig. 1, the proximal pressure measurement device may be a guide catheter 100 (described later) for measuring pressure within the blood vessel near the proximal side 30a and generating a pressure signal. The examples of the present disclosure are not limited thereto and the proximal pressure measurement device may be other devices to obtain intravascular pressure near the proximal side 30 a.

In some examples, as shown in fig. 1, the guide catheter 100 may be elongate tubular and the guide catheter 100 may have an internal cavity 101. In some examples, the guide catheter 100 has a proximal side 100a proximal to the host 30 (described later) and a distal side 100b distal to the host 30.

In some examples, the guide catheter 100 is provided with a first pressure sensor 102.

In some examples, the first pressure sensor 102 may be an invasive blood pressure sensor that may be directly connected to a port of the proximal side 100a of the guide catheter 100 so as to be disposed on the guide catheter 100. For example, the first pressure sensor 102 may be provided with a circular interface matching the tubular structure of the guide catheter 100 for connection with the guide catheter 100. This allows a better matching of the guide catheter 100 and the first pressure sensor 102, and a better measurement of the intravascular pressure.

In some examples, the first pressure sensor 102 may sense the pressure generated by the flow of liquid from the distal side 100b into the interior cavity 101 of the guide catheter 100. In some examples, during operation of the system 1, the guide catheter 100 may acquire a first initial pressure signal (e.g., a first pressure signal and a third pressure signal described later) within the blood vessel proximate the proximal side 30a (relative to a second pressure sensor 112 described later) at a sampling rate via the first pressure sensor 102.

In some examples, the guide catheter 100 may generate a first initial pressure signal by acquiring pressure within the blood vessel near the proximal side 30a at a first sampling rate by the first pressure sensor 102. For example, the guide catheter 100 may be placed in a blood vessel of a human body and the port of the distal side 100b of the guide catheter 100 is placed at a location within the blood vessel near the proximal side 30a (also referred to as a "first location", e.g. the proximal coronary artery 401 in fig. 4), the first pressure sensor 102 may be placed outside the body and connected to the port of the proximal side 100a of the guide catheter 100, blood at the first location within the blood vessel may flow into the guide catheter 100 and may flow from the distal side 100b of the guide catheter 100 to the proximal side 100a of the guide catheter 100 to be sensed by the first pressure sensor 102, whereby the first pressure sensor 102 is able to obtain the pressure within the interior cavity 101 of the guide catheter 100, i.e. the pressure at the location within the blood vessel near the proximal side 30a (first location), and generate a first initial pressure signal. For example, the guiding catheter 100 may acquire a cardiac cycle-varying pressure within the blood vessel proximal to the proximal side 30a via the first pressure sensor 102 at a first sampling rate and generate a first pressure signal.

In other examples, the first pressure sensor 102 may be a capacitive pressure sensor, a resistive pressure sensor, a fiber optic pressure sensor, etc., the first pressure sensor 102 may be disposed on the distal side 100b of the guide catheter 100, e.g., the first pressure sensor 102 may be disposed on an outer wall of the guide catheter 100. In operation of the system 1, the guide catheter 100 may be placed within a blood vessel of a human body and the first pressure sensor 102 may be placed within the blood vessel at a location proximal to the proximal side 30 a. In this case, the first pressure sensor 102 may directly sense the pressure at a location within the blood vessel proximal to the proximal side 30a (first location) and generate a first initial pressure signal.

In some examples, the proximal pressure measurement device may be coupled to the withdrawal device 20, e.g., the guide catheter 100 may be coupled to the withdrawal device 20 and the first pressure sensor 102 may be coupled to the withdrawal device 20 via a transmission wire. In this case, the first initial pressure signal (for example, a first pressure signal and a third pressure signal described later) obtained by measurement of the first pressure sensor 102 is transmitted to the retracting device 20 via the transmission wire.

In some examples, if the proximal pressure measurement device is a guide catheter 100, the diameter of the interior cavity 101 of the guide catheter 100 may be greater than the outer diameter of the distal pressure measurement device (described later). In some examples, the distal pressure measurement device may enter the internal cavity 101 from the proximal side 100a of the guide catheter 100 (see fig. 1 and 3). In this case, a blood pressure measurement catheter 110 (described later) can be disposed within the internal cavity 101 when the system 1 is in operation.

In some examples, the blood pressure measurement device 10 may include a distal pressure measurement device. In some examples, as shown in fig. 1, the distal pressure measurement device may be a blood pressure measurement catheter 110 (described later), but examples of the present disclosure are not limited thereto, as the distal pressure measurement device may be other devices for measuring intravascular pressure away from the proximal side 30a, such as a medical guidewire with a pressure sensor.

In some examples, as shown in fig. 1 and 2, the blood pressure measurement catheter 110 may be elongate, tubular, and the outer diameter of the blood pressure measurement catheter 110 may be smaller than the inner diameter of the guide catheter 100, that is, the outer diameter of the blood pressure measurement catheter 110 is smaller than the internal cavity 101. This enables a better positioning of the blood pressure measuring catheter 110 within the guiding catheter 100 and facilitates a movement of the blood pressure measuring catheter 110 relative to the guiding catheter 100, which guiding catheter 100 may remain stationary.

In some examples, as shown in fig. 1 and 2, blood pressure measurement catheter 110 may have a proximal side 110a proximal to host computer 30 and a distal side 110b distal to host computer 30, and blood pressure measurement catheter 110 may have an internal cavity 111. In some examples, as shown in fig. 1, the blood pressure measurement catheter 110 may be provided with a second pressure sensor 112, and the second pressure sensor 112 may be provided at a distal side 110b of the blood pressure measurement catheter 110. In some examples, the second pressure sensor 112 may be disposed on an outer wall of the blood pressure measurement catheter 110, and in some examples, the second pressure sensor 112 may also be disposed within an interior cavity 111 of the blood pressure measurement catheter 110, the interior cavity 111 may have a window with the second pressure sensor 112. In this case, the second pressure sensor 112 can be made to measure the pressure in the blood vessel to generate pressure signals (e.g., a second pressure signal and a fourth pressure signal described later) when the system 1 is operated.

In some examples, the blood pressure measurement catheter 110 may be guided along the guide catheter 100 to a preset position (also referred to as a "second position"), i.e., a position within the blood vessel distal to the distal side 30b (e.g., the distal coronary artery 402 in fig. 4) relative to the first pressure sensor 102. Specifically, during interventional procedures, an operator such as a medical staff member first advances the guide catheter 100 from a site on the patient (or patient) (e.g., at the femoral artery of fig. 3) along the blood vessel to a first position within the blood vessel, for example, as shown in fig. 3, where the port on the distal side 100b of the guide catheter 100 is placed within the first position within the blood vessel, and then advances a medical guidewire (not shown) further along the guide catheter 100 to a depth of the blood vessel, e.g., a preset position, by, for example, contrast imaging with a contrast agent. In this case, the blood pressure measuring catheter 110 is along the medical guidewire and the blood pressure measuring catheter 110 is moved by operating (e.g. pushing and/or pulling) the proximal side 110a of the blood pressure measuring catheter 110 outside the patient until the blood pressure measuring catheter 110 is guided to a preset position, i.e. the second pressure sensor 112 is guided to a preset position, whereby the second pressure sensor 112 is able to measure the pressure at a preset position within the blood vessel.

In some examples, as shown in fig. 3 and 4, in operation of the system 1, the blood pressure measurement catheter 110 may be disposed within the interior cavity 101 of the guide catheter 100, and the blood pressure measurement catheter 110 may be movable relative to the guide catheter 100, e.g., by pushing the proximal side 110a or a device coupled to the proximal side 110a to advance the blood pressure measurement catheter 110 along the medical guidewire deep into a blood vessel within a patient to enable the second pressure sensor 112 to measure pressure at a predetermined location within the blood vessel.

In some examples, the distal side 110b of the blood pressure measurement catheter 110 may be deeper into the patient relative to the distal side 100b of the guide catheter 100, i.e., the second pressure sensor 112 may generate a second initial pressure signal (e.g., a second pressure signal and a fourth pressure signal described later) relative to the first pressure sensor 102 measuring pressure within the blood vessel further from the proximal side 30 a.

In some examples, the first location may be a side of the coronary artery 400 proximate the aortic port (e.g., the proximal coronary artery 401) and the second location may be a side of the coronary artery 400 distal the aortic port (e.g., the distal coronary artery 402).

In some examples, an X-ray opaque developer ring may be provided on at least one side of the second pressure sensor 112. However, examples of the present disclosure are not limited thereto, and an X-ray opaque developing ring may be provided at the distal end side 110b of the blood pressure measurement catheter 110, and the second pressure sensor 112 may be provided on the X-ray opaque developing ring. In this case, the position of the second pressure sensor 112 within the blood vessel can be determined.

In some examples, the blood pressure measurement catheter 110 may acquire pressure at a preset location via the second pressure sensor 112 at a first sampling rate and generate a second pressure signal. In some examples, blood pressure measurement catheter 110 is in a resting state when the second pressure signal is acquired. That is, in operation of the system 1, the second pressure sensor 112 may be directed to a preset location, and the second pressure sensor 112 may measure the pressure within the vessel at the first sampling rate that varies with the cardiac cycle at the preset location and generate a second pressure signal.

In some examples, as shown in fig. 1 and 2, a blood pressure measurement catheter 110 may be coupled to the retraction device 20. The blood pressure measurement catheter 110 may be provided with a signal path 113, the signal path 113 may be provided within the internal cavity 111 of the blood pressure measurement catheter 110, and the signal path 113 may connect the second pressure sensor 112 and the withdrawal device 20. In this case, a second initial pressure signal (for example, a second pressure signal and a fourth pressure signal described later) obtained by measurement of the second pressure sensor 112 is transmitted to the extracorporeal withdrawal device 20 via the signal path 113.

In some examples, the second pressure sensor 112 may be a capacitive pressure sensor, a resistive pressure sensor, a fiber optic pressure sensor, or the like. In addition, the second pressure sensor 112 may be a MEMS pressure sensor. For example, the second pressure sensor 112 may measure in a range of about-50 mmHg to about +300 mmHg. Depending on the type of second pressure sensor 112, signal path 113 may be a conductive medium such as an electrical lead. Further, in some embodiments, the signal path 113 may also be a wireless communication line, an infrared communication line, or an ultrasonic communication line.

In the present disclosure, blood pressure measurement catheter 110 and guide catheter 100 may be separately advanced into or withdrawn from the patient as separate devices. In this case, the doctor can control the blood pressure measuring catheter 110 and the guide catheter 100 independently. For example, during operation of the system 1, a healthcare worker may control movement of the blood pressure measurement catheter 110 relative to the guide catheter 100 (e.g., advancement or retraction deep into a blood vessel within a patient), and the guide catheter 100 may remain stationary. By having the blood pressure measurement catheter 110 and the guide catheter 100 as separate devices, it is possible for a medical person to more easily operate the blood pressure measurement catheter 110, enabling the blood pressure measurement catheter 110 to measure the intravascular pressure (e.g., the second pressure signal and a fourth pressure signal described later) distal from the proximal side 30 a.

In some examples, the second pressure sensor 112 may measure the pressure within the respective vessel and generate the respective pressure signal simultaneously with the first pressure sensor 102 at the same sampling rate, e.g., the first pressure sensor 102 measures a first initial pressure signal while the second pressure sensor 112 measures a second initial pressure signal. In some examples, the pressure value corresponding to the first initial pressure signal ("first initial pressure value") and the pressure value corresponding to the second pressure signal (also referred to as "second initial pressure value") may be in one-to-one correspondence.

In some examples, the first and second initial pressure signals may include blood vessel pressure (also referred to as "intravascular pressure") corresponding to one or more cardiac cycles (see fig. 5).

In some examples, the first pressure sensor 102 and the second pressure sensor 112 are in a stationary state. The first pressure sensor 102 measures pressure at a first location at a first sampling rate to generate a first pressure signal, while the second pressure sensor 112 measures pressure at a second location at the first sampling rate to generate a second pressure signal. In some examples, the pressure value corresponding to the first pressure signal (also referred to as a "first pressure value") and the pressure value corresponding to the second pressure signal (also referred to as a "second pressure value") may be in one-to-one correspondence.

In some examples, the first sampling rate may range from about 30Hz to 1.5KHz. For example, the second pressure sensor 112 may measure the pressure within the respective blood vessel simultaneously with the first pressure sensor 102 at a sampling rate of 30Hz, 50Hz, 100Hz, 200Hz, 250Hz, 300Hz, 400Hz, 500Hz, 600Hz, 700Hz, 1000Hz, 1100Hz, 1200Hz, 1300Hz, 1400Hz, 1500 Hz. Preferably, the second pressure sensor 112 and the first pressure sensor 102 may be measured simultaneously at a sampling rate of 250 Hz.

In some examples, the first pressure signal and the second pressure signal may comprise blood pressure of a blood vessel (also referred to as "intravascular pressure") corresponding to one or more cardiac cycles (see fig. 5). In some examples, the first pressure signal and the second pressure signal include at least intravascular pressure corresponding to one complete cardiac cycle.

In some examples, the first pressure sensor 102 and the second pressure sensor 112 in the blood pressure measurement device 10 may simultaneously measure the pressure within the blood vessel and generate respective pressure signals (e.g., first pressure signal and second pressure signal, third pressure signal and fourth pressure signal, which may be described), and the retraction device 20 may be coupled to the blood pressure measurement device 10 and receive the pressure signals from the blood pressure measurement device 10.

In some examples, the blood pressure measurement device 10 may measure the pressure at the first and second locations within the blood vessel simultaneously and generate the first and second pressure signals.

In some examples, the withdrawal device 20 may be connected to the blood pressure measurement device 10 and receive the first and second pressure signals, that is, the withdrawal device 20 may be connected to the guide catheter 100 and receive the first pressure signal from the guide catheter 100, and the withdrawal device 20 may be connected to the blood pressure measurement catheter 110 and receive the second pressure signal from the blood pressure measurement catheter 110.

In some examples, as the blood pressure measurement catheter 110 moves relative to the guide catheter 100, for example, the blood pressure measurement catheter 110 enters into the blood vessel along the guide catheter 100 and is guided deep into the blood vessel, the second pressure sensor 112 may drift during the movement of the blood pressure measurement catheter 110, so that errors occur in the measurement of the second pressure sensor 112, and the second pressure sensor 112 may be corrected and verified.

In some examples, during operation of the system 1, the intravascular pressure measured by the first pressure sensor 102 and the second pressure sensor 112 and the generated pressure signals (e.g., the first initial pressure signal and the second initial pressure signal) may be received by the pullback device 20 and then transmitted to the host 30 for processing, and the host 30 may display a time-dependent pressure profile (described later) corresponding to the pressure signals.

In some examples, the second pressure sensor 112 may be placed in the first position to measure blood vessel pressure before the second pressure sensor 112 is placed in the second position to measure the second pressure signal, i.e., the second pressure sensor 112 may measure the intravascular pressure at the same location (e.g., the first location) as the first pressure sensor 102, thereby correcting the second pressure sensor 112. Specifically, before the second pressure sensor 112 is guided to the preset position (e.g., the distal coronary artery 402), the second pressure sensor 112 may be calibrated first, and the second pressure sensor 112 may be placed at the first position (e.g., the proximal coronary artery 401), in which case, the second pressure sensor 112 may measure the intravascular pressure at the same position (e.g., the first position) as the first pressure sensor 102, and the second pressure sensor 112 may be calibrated based on the pressure signal measured by the first pressure sensor 102, until there is no significant difference between the pressure signals obtained by the second pressure sensor 112 and the first pressure sensor 102, that is, the two corresponding change curves displayed on the host 30 coincide.

In some examples, after correction by the second pressure sensor 112, the healthcare worker may move the blood pressure measurement catheter 110 (e.g., advance deep into a blood vessel within the patient) by manipulating (e.g., pushing) the proximal side 110a of the blood pressure measurement catheter 110 external to the patient (or a device coupled to the proximal side 110a of the blood pressure measurement catheter 110) to place the second pressure sensor 112 at a second location (e.g., the distal coronary artery 402) to obtain a second pressure signal. In this case, the first pressure signal obtained by the second pressure sensor 112 can be made more accurate and can be matched with the second pressure signal, and it can be convenient to better determine the pathological condition of the blood vessel to be measured (i.e., the blood vessel measured by the first pressure sensor 102 and the second pressure sensor 112, such as the coronary artery 400 in fig. 4) later.

In some examples, after the second pressure sensor 112 is placed in the second position to measure the first pressure signal, the second pressure sensor 112 may be placed again in the first position to measure the blood pressure of the blood vessel, and the second pressure sensor 112 may be verified. Specifically, after the second pressure sensor 112 is placed at the preset position to obtain the second pressure signal, the second pressure sensor 112 may be verified, and the blood pressure measurement catheter 110 may be retracted by the retraction device 20 (described later) or manually (e.g., a medical person may pull the proximal side 110a of the blood pressure measurement catheter 110) to place the second pressure sensor 112 at the first position (e.g., the proximal coronary artery 401). In this case, the second pressure sensor 112 may measure the intravascular pressure at the first position simultaneously with the first pressure sensor 102, and based on the pressure signal measured by the first pressure sensor 102, it may be verified whether the second pressure sensor 112 drifts during the movement, i.e. it is verified whether an error occurs in the second pressure sensor 112. For example, if there is no significant difference between the pressure signals measured by the first pressure sensor 102 and the second pressure sensor 112 at the first position, it may be determined that the pressure signal (e.g., the second pressure signal) obtained by the measurement of the second pressure sensor 112 can be used normally. If there is a significant difference between the pressure signals measured by the first pressure sensor 102 and the second pressure sensor 112 at the first position, it may be determined that the pressure signal (e.g., the second pressure signal) obtained by the measurement by the second pressure sensor 112 is unusable and the accuracy of the measured pressure signal cannot be determined, in which case the pressure signal required for the measurement may be re-performed.

In some examples, as shown in fig. 1 and 2, the system 1 may include a retraction device 20. The withdrawal device 20 may be connected to the blood pressure treatment device 310. The withdrawal device 20 can be disposed outside the body.

In some examples, as shown in fig. 1, the retraction device 20 can include a drive module 201, a switch module 202, and a signal receiving module 203.

In some examples, the withdrawal device 20 may be connected to a distal pressure measurement device in the blood pressure treatment device 310. For example, the withdrawal device 20 may be connected to the blood pressure measurement catheter 110, and the withdrawal device 20 may have a port that mates with the proximal side 110a of the blood pressure measurement catheter 110. In some examples, the drive module 201 in the retraction device 20 can control movement (e.g., retraction) of the blood pressure measurement catheter 110 within the blood vessel relative to the guide catheter 100. In some examples, host computer 30 may adjust the rate of retraction of blood pressure measurement catheter 110 within the blood vessel by controlling drive module 201.

In some examples, the retraction device 20 can include a switch module 202, and the switch module 202 can be used to control the operating state of the drive module 201. For example, if the switch module 202 is in an on state, the driving module 201 can control the blood pressure measurement catheter 110 to retract automatically. If the switch module 202 is in the off state, the drive module 201 is deactivated, at which time manual retraction is enabled, e.g., a medical professional may control retraction of the blood pressure measurement catheter 110 by pulling on the proximal side 110a of the blood pressure measurement catheter 110 or a device connected to the proximal side 110 a.

In some examples, the withdrawal device 20 may be connected to the guide catheter 100, and the signal receiving module 203 in the withdrawal device 20 may receive a first initial pressure signal (e.g., a first pressure signal or a third pressure signal described later) from the guide catheter 100. In some examples, the retraction device 20 may be connected to the blood pressure measurement catheter 110, and the signal receiving module 203 in the retraction device 20 may receive a second initial pressure signal (e.g., a second pressure signal or a fourth pressure signal described later) from the blood pressure measurement catheter 110.

In some examples, the retraction device 20 may be configured to control retraction of the blood pressure measurement catheter 110 and cause the first pressure sensor 102 to measure the pressure within the blood vessel (e.g., the intravascular pressure at the first location) at the second sampling rate to obtain the third pressure signal and the second pressure sensor 112 to measure the pressure within the blood vessel at the second sampling rate to obtain the fourth pressure signal. Thereby, a third pressure signal and a fourth pressure signal can be obtained. Specifically, the retraction device 20 may generate a third pressure signal by measuring the pressure at a location within the blood vessel proximal to the proximal side 30a (e.g., a first location) at a second sampling rate during control of retraction of the blood pressure measurement catheter 110, and the second pressure sensor 112 may generate a fourth pressure signal by measuring the pressure within the blood vessel (e.g., a pressure within the blood vessel distal to the proximal side 30 a) at a second sampling rate during retraction of the blood pressure measurement catheter 110.

In some examples, as shown in fig. 1 and 2, the system 1 may include a host 30. The host 30 may be coupled to the retractor 20. In some examples, the host 30 may receive pressure signals (e.g., first and second pressure signals, third and fourth pressure signals, etc.) transmitted by the pullback device 20.

In some examples, as shown in fig. 1 and 2, the host 30 may include an image processing device 300 and a blood pressure processing device 310. In some examples, the image processing apparatus 300 may be connected with the blood pressure processing apparatus 310. In some examples, the blood pressure processing device 310 may be coupled to the withdrawal device 20. In some examples, the blood pressure processing device 310 may receive the pressure signal transmitted by the retraction device 20.

In some examples, the blood pressure processing device 310 may control the retraction device 20, e.g., control whether the retraction device 20 is retracted. In some examples, the host 30 may determine whether the retraction device 20 is capable of retracting by itself, and may determine whether the blood pressure measurement device 10 is capable of stable measurement by the pressure signal received by the host 30, and if the blood pressure measurement device 10 is capable of stable measurement, the host 30 may control the retraction device 20 to retract. In some examples, configuring the blood pressure measurement device 10 is complete, e.g., the blood pressure measurement device 10 may measure the pressure within the blood vessel near the proximal side 30a and the pressure within the blood vessel far from the proximal side 30a and generate pressure signals, and the host computer 30 may calculate the respective variances of the pressure signals based on the received pressure signals to determine whether the blood pressure measurement device 10 is capable of stable measurement. However, examples of the present disclosure are not limited thereto, and in some examples, the pressure signal received by the host computer 30 may be compared with an electrocardiogram obtained at the same time (for example, whether the blood pressure measurement device 10 is capable of stable measurement may be determined by whether the trend of the electrocardiogram and the pressure signal are correlated).

In some examples, the image processing apparatus 300 may be an X-ray machine. In some examples, prior to intervention of the blood pressure measurement device 10 within a blood vessel, a contrast agent may be injected into a patient, an X-ray contrast image of the blood vessel region under test may be obtained using the image processing device 300 and a first image signal may be generated and transmitted to the blood pressure processing device 310, and the blood pressure processing device 310 may receive the first image signal and store it.

In some examples, the X-ray contrast image may include a plurality of coronary arteries, which may be sequentially processed, i.e., coronary artery 400 in the X-ray contrast image may be processed one by one, thereby enabling determination of the overall lesion of the blood vessel of the patient.

In some examples, the position of the image processing device 300 may be kept unchanged, the blood pressure measuring device 10 is inserted into the blood vessel to be measured, and the image processing device 300 may obtain a real-time image of the blood pressure measuring catheter 110 containing the developing ring in the blood vessel by X-rays. For example, as the blood pressure measurement catheter 110 is moved (e.g., retracted) within the blood vessel, the image processing apparatus 300 may obtain real-time images of the blood pressure measurement catheter 110 containing the visualization loop at different locations within the blood vessel via X-rays. In some examples, the image processing device 300 may generate a second image signal from the obtained real-time image and transmit the second image signal to the blood pressure processing device 310.

In some examples, host computer 30 may set a retraction endpoint based on the X-ray contrast image (i.e., preset a corresponding location in the X-ray contrast image), and retraction device 20 may control blood pressure measurement catheter 110 to retract to the retraction endpoint and stop retraction. That is, the retraction device 20 can control the retraction of the blood pressure measuring catheter 110 to a predetermined corresponding position in the X-ray contrast image. Thereby enabling the blood pressure measuring catheter 110 to be automatically retracted to a preset corresponding position.

In some examples, the blood pressure processing device 310 may determine whether the blood pressure measurement catheter 110 is retracted to a retraction endpoint based on the first image signal and the second image signal, and if the blood pressure measurement catheter 110 is retracted to the retraction endpoint (e.g., a developing ring on the blood pressure measurement catheter 110 is less than or equal to a predetermined distance from the retraction endpoint), the host computer 30 controls the retraction device 20 to stop the retraction.

In some examples, the withdrawal endpoint (preset corresponding position) may be selected by the physician on the X-ray contrast image at his own discretion. In some examples, the retraction end point (preset corresponding position) may correspond to a bifurcation point of a blood vessel or an end of a blood vessel in an X-ray contrast image, for example, the corresponding position may be set as a first position in the X-ray contrast image. Whereby the corresponding position can be determined. In some examples, the retraction endpoint may be further away from distal side 30a relative to the location (e.g., first location) where first pressure sensor 102 measures the pressure of the blood vessel, thereby enabling second pressure sensor 112 to measure the pressure within the blood vessel distal from distal side 30 a.

In some examples, the distal side 100b of the guide catheter 100 (i.e., at the port of the distal side 100 b) may be provided with a developing ring, the port of the distal side 100b may be used as a withdrawal endpoint, the withdrawal device 20 may control the blood pressure measurement catheter 110 to withdraw until the distance between the developing ring on the blood pressure measurement catheter 110 and the developing ring on the guide catheter 100 is equal to or less than a predetermined distance, and the host computer 30 controls the withdrawal device 20 to stop withdrawing.

In some examples, host computer 30 may calculate a measured length of the vessel from the width of the visualization loop, the X-ray contrast image, and the real-time image. Specifically, the host computer 30 may obtain a ratio of the width of the developing ring in the real-time image to the width of the actual developing ring according to the real-time image and the width of the developing ring along the length direction of the blood pressure measuring catheter 110, and obtain a ratio of the width of the developing ring in the real-time image to the occupied ratio of the width of the developing ring in the X-ray contrast image in the region of the blood vessel to be measured according to the real-time image and the X-ray contrast image, thereby being capable of calculating the measured length of the blood vessel in the X-ray contrast image. For example, host computer 30 may calculate the length of blood pressure measurement catheter 110 withdrawn from an initial position (e.g., the second position) to a withdrawal endpoint (e.g., the first position).

In some examples, the host 30 may control the withdrawal speed of the withdrawal device 20 based on the measured length. In other examples, a healthcare worker may use the host 30 to set the withdrawal speed of the withdrawal device 20 by himself. For example, the retracting means 20 is provided to retract at a uniform speed.

In some examples, the retraction device 20 is configured to control retraction of the blood pressure measurement catheter 110, and the host computer 30 may calculate a retraction time of the blood pressure measurement catheter 110 based on the measured length and the retraction speed. Thereby enabling the withdrawal time of the blood pressure measuring catheter 110 to be obtained.

In some examples, the host 30 may be coupled to the retraction device 20 and receive pressure signals (e.g., first and second pressure signals, third and fourth pressure signals, etc.) transmitted by the retraction device 20.

In some examples, the host 30 may include a blood pressure processing device 310, the blood pressure processing device 310 may include a pre-processing module and a computing module, and the blood pressure processing device 310 may process the received pressure signal.

In some examples, the host 30 may receive a first initial pressure signal and a second initial pressure signal, and the host 30 may obtain the target ratio based on the first initial pressure signal and the second initial pressure signal. In some examples, host 30 may control whether first pressure sensor 102 and second pressure sensor 112 are operational, such as collecting pressure signals. In some examples, the host 30 may control whether the retraction device 20 is retracted.

In some examples, while system 1 is in operation, blood pressure measurement catheter 110 may be in a stationary state, host 30 may control first pressure sensor 102 and second pressure sensor 112 to take pressure measurements within the blood vessel at a sampling rate, first pressure sensor 102 may take pressure within the blood vessel proximate proximal side 30a (first location, e.g., proximal coronary artery 401) at a first sampling rate and generate a first pressure signal, second pressure sensor 112 may take pressure at a preset location within the blood vessel (second location, e.g., distal coronary artery 402) at a first sampling rate and generate a second pressure signal, and the first pressure signal and second pressure signal may be transmitted to retraction device 20 for processing by host 30 to obtain a first target ratio. It is thereby possible to determine whether a lesion exists in a blood vessel without injecting a congestion inducing drug.

In some examples, during operation of system 1, retraction device 20 is configured to control retraction of blood pressure measurement catheter 110 and cause first pressure sensor 102 to measure the pressure within the blood vessel and generate a third pressure signal at the second sampling rate and second pressure sensor 112 to measure the pressure within the blood vessel and generate a third pressure signal at the second sampling rate. Specifically, in operation of the system 1, the retraction device 20 is configured to control retraction of the blood pressure measurement catheter 110, the blood pressure measurement catheter 110 in a retracted state, the guide catheter 100 in a stationary state, the host 30 may control the first pressure sensor 102 and the second pressure sensor 112 to take pressure measurements within the blood vessel at a sampling rate, the first pressure sensor 102 may take pressure within the blood vessel near the proximal side 30a (first location, e.g., the proximal coronary artery 401) and generate a third pressure signal at a second sampling rate, and the second pressure sensor 112 may take pressure within the corresponding blood vessel (e.g., the blood vessel distal from the proximal side 30 a) and generate a fourth pressure signal at the second sampling rate during retraction of the blood vessel. The third pressure signal and the fourth pressure signal may be transmitted to the pullback device 20 and further transmitted to the host 30 for processing to obtain a second target ratio.

In other examples, during operation of the system 1, the retraction device 20 is configured to control retraction of the blood pressure measurement catheter 110, and the first pressure sensor 102 measures intravascular pressure at a sampling rate and generates a pressure signal that can be transmitted to the retraction device 20 and, in turn, to the host 30 for processing.

In some examples, the second pressure sensor 112 and the first pressure sensor 102 may simultaneously measure and obtain the third pressure signal and the fourth pressure signal at the second sampling rate. In some examples, the pressure value corresponding to the third pressure signal (third pressure value) and the pressure value corresponding to the fourth pressure signal (fourth pressure value) may be in one-to-one correspondence.

In some examples, the blood pressure processing apparatus 310 includes a preprocessing module that can generate a waveform map based on pressure signals (e.g., first and second pressure signals, third and fourth pressure signals, etc.) received by the host 30, which can be displayed in the form of waveforms on, for example, a display screen. Wherein the vertical axis of the waveform graph may be the magnitude of the pressure (i.e., the pressure value), and the horizontal axis of the waveform graph may be the time axis.

In some examples, the preprocessing module may reject significantly invalid signals, e.g., the maximum value (or average, peak-to-peak) of the second pressure signal is greater than 125% of the maximum value (or average, peak-to-peak) of the first pressure signal. In some examples, the preprocessing module may automatically synchronize the received pressure signals, e.g., there is a short delay between peaks of the first pressure signal and the second pressure signal, and the preprocessing module may automatically synchronize the first pressure signal and the second pressure signal.

Fig. 5 is a pressure waveform diagram illustrating a plurality of cardiac cycles to which examples of the present disclosure relate. Fig. 6 is a pressure waveform diagram illustrating one cardiac cycle of fig. 5 in relation to an example of the present disclosure. Fig. 7 is a pressure waveform diagram illustrating one cardiac cycle of fig. 5 in accordance with another example of the present disclosure.

In some examples, the blood pressure measurement device 10 measures obtained pressure signals (e.g., a first initial pressure signal and a second initial pressure signal) may include intravascular pressure of one or more cardiac cycles (see fig. 5).

In some examples, the host computer 30 may process the received first and second initial pressure signals to obtain the target ratio by a pre-configured processing scheme. In some examples, the first initial pressure signal received by the host 30 may be a first pressure signal, the second initial pressure signal received by the host 30 may be a second pressure signal, and the host 30 may process the first pressure signal and the second pressure signal to obtain a first target ratio. In some examples, the first initial pressure signal received by the host 30 may be a third pressure signal, the second initial pressure signal received by the host 30 may be a fourth pressure signal, and the host 30 may process the third pressure signal and the fourth pressure signal to obtain a second target ratio.

In some examples, the preprocessing module may obtain a first waveform map including at least one complete cardiac cycle based on a first initial pressure signal (e.g., a first pressure signal) and a second initial pressure signal (e.g., a second pressure signal), the first waveform map including a first change profile of the first initial pressure signal over time and a second change profile of the second initial pressure signal over time. Thereby, a first waveform diagram can be obtained. That is, the preprocessing module may obtain a first waveform map based on the first initial pressure signal and the second initial pressure signal, the first waveform map including a first variation curve and a second variation curve, the first waveform map may include one or more cardiac cycles. The preprocessing module may obtain a first change curve of a pressure value corresponding to the first initial pressure signal (also referred to as a "first initial pressure value") over time based on the first initial pressure signal, and the preprocessing module may obtain a second change curve of a pressure value corresponding to the second initial pressure signal over time based on the second initial pressure signal. For example, as shown in fig. 5, the host 30 receives a first initial pressure signal and a second initial pressure signal comprising a succession of multiple cardiac cycles and may generate a waveform map. In fig. 5, curve a is a time-varying curve of the first initial pressure signal (i.e., the pressure value corresponding to the first initial pressure signal), and curve B is a time-varying curve of the second initial pressure signal (i.e., the pressure value corresponding to the second initial pressure signal). A plurality of first initial pressure values over a plurality of cardiac cycles and a second initial pressure value corresponding to each of the first initial pressure values may be obtained from the curve A, B.

In some examples, a method of tracking a cardiac cycle event using blood pressure may include calculating a ratio of a pressure value of a second initial pressure signal to a pressure value of a first initial pressure signal corresponding to a pressure value of the second initial pressure signal based on the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio.

In some examples, the blood pressure processing apparatus 310 includes a computing module that may further process the waveform map generated by the preprocessing module to obtain a new waveform map.

In some examples, the computing module may determine a cardiac cycle based on the first waveform map and obtain a mean value of a first initial pressure signal corresponding to the cardiac cycle, an initial pressure ratio of a pressure value of a second initial pressure signal to a pressure value of the first initial pressure signal corresponding to the second initial pressure signal, and a derivative of the second initial pressure signal with respect to time based on the first waveform map. Specifically, the computing module may determine one or more cardiac cycles included in the first waveform map based on the first waveform map and process each cardiac cycle. The calculation module may select any cardiac cycle, obtain a mean value of first initial pressure values and a mean value of second initial pressure values corresponding to the cardiac cycle based on a first change curve and a second change curve in the cardiac cycle, and obtain initial pressure ratios of a plurality of second initial pressure values in the cardiac cycle to first initial pressure values corresponding to the respective second initial pressure values based on the first change curve and the second change curve in the cardiac cycle. The calculation module may also obtain a derivative of the second initial pressure value with respect to time based on the second change curve.

In some examples, the first intersection point (described in detail later) may be obtained from the average of the pressure values of the first initial pressure signal and the first initial pressure signal. In some examples, the first midpoint time and the second midpoint time may be obtained from a derivative of the second initial pressure signal with respect to time and the second initial pressure signal (described in detail later).

In some examples, the calculation module may generate a third change curve corresponding to a mean value of the first initial pressure signal over the cardiac cycle, a fourth change curve of the initial pressure ratio over time over the cardiac cycle, and a fifth change curve corresponding to a derivative of the second initial pressure signal in the first waveform map to obtain a second waveform map including the first change curve, the second change curve, the third change curve, the fourth change curve, and the fifth change curve. Thereby, a second waveform diagram can be obtained. Specifically, the calculation module may generate a third variation curve in the first waveform diagram based on the average of the obtained first initial pressure values (see curve D in fig. 6), the calculation module may obtain a fourth variation curve of the initial pressure ratio over time based on initial pressure ratios of the obtained plurality of second initial pressure values and the first initial pressure values corresponding to the respective second initial pressure values (see curve C in fig. 6, wherein the curve C shows a pressure ratio that is one hundred times the actually calculated pressure ratio), and the calculation module may obtain a fifth variation curve of the derivative over time based on the derivative of the obtained second initial pressure values with respect to time (see curve E in fig. 7). For example, as shown in fig. 6, a curve a is a curve of time variation of a first initial pressure signal (i.e., a pressure value corresponding to the first initial pressure signal), a curve B is a curve of time variation of a second initial pressure signal (i.e., a pressure value corresponding to the second initial pressure signal), a curve C is a curve of time variation of an initial pressure ratio of the second initial pressure value to the first initial pressure value corresponding to each second initial pressure value, and a curve D is a curve generated by a mean value of the first initial pressure values. As shown in fig. 7, a curve a is a time-varying curve of a first initial pressure signal (i.e., a pressure value corresponding to the first initial pressure signal), a curve B is a time-varying curve of a second initial pressure signal (i.e., a pressure value corresponding to the second initial pressure signal), a curve C is a time-varying curve of an initial pressure ratio of the second initial pressure value to the first initial pressure value corresponding to each of the second initial pressure values (wherein the curve C shows a pressure ratio that is hundreds of times the actually calculated pressure ratio), and a curve E is a curve generated by a derivative of the second initial pressure value with respect to time (wherein a value corresponding to an ordinate of the curve E is referred to a right ordinate axis of fig. 7). In some examples, the host 30 may select a desired change curve based on a particular manner of acquisition of a subsequent target ratio (e.g., a first target ratio), and may not acquire all of the change curves described above (described later). In some examples, the fifth variation curve may be smoothed.

As described above, after the calculation module processes the first waveform diagram, a new change curve can be generated on the basis of the first waveform diagram, so that the target ratio can be conveniently obtained subsequently.

In some examples, the second waveform map includes characteristic information, which may include a first intersection (e.g., point m in fig. 6) of a fall time period of the first variation curve and a third variation curve within a selected cardiac cycle (e.g., the selected cardiac cycle may be referred to as interval a in fig. 6), that is, the characteristic information includes the first intersection, which is an intersection of the first variation curve and the third variation curve and the intersection is at the fall time period of the first variation curve.

In some examples, the characteristic information may include a first midpoint time corresponding to a midpoint of a time period from a minimum of the fifth change curve to a maximum of the second change curve within the selected cardiac cycle (see time corresponding to line L1 in fig. 7, i.e., corresponding horizontal axis coordinates). In some examples, the characteristic information may include a second midpoint time corresponding to a midpoint of a time period from a maximum of the fifth change curve to a maximum of the second change curve within the selected cardiac cycle (see time corresponding to line L2 in fig. 7). Thereby facilitating subsequent target ratio values. In some examples, the characteristic information may be determined according to a specific manner of acquiring the subsequent target ratio and the selected change curve, and all the characteristic information may not be acquired.

In some examples, the blood pressure processing device 310 may process the first initial pressure signal and the second initial pressure signal to obtain the target ratio.

In some examples, the target ratio (e.g., the first target ratio) may be an average of a predetermined number of initial pressure ratios corresponding to a selected cardiac cycle (e.g., the selected cardiac cycle may be referred to as interval a in fig. 6), an average of a predetermined number of initial pressure ratios corresponding to a diastolic period in the cardiac cycle, an average of a corresponding pressure ratio in a period (second preset period) from a first intersection point to a minimum value of the first initial pressure signal in the cardiac cycle, a corresponding minimum pressure ratio in a period (first preset period) from a first intersection point to a first initial pressure signal in which the first initial pressure signal is in a continuously decreasing period (first preset period), a pressure ratio in a period (second preset period) from a first intersection point to a minimum value of the first initial pressure signal in the cardiac cycle corresponding to a midpoint in the cardiac cycle corresponding to a first intersection point in a period (third preset period) at 80% of the cardiac cycle, an average of a corresponding pressure ratio in a period (first intersection point in the cardiac cycle) to a first initial pressure signal in a first intersection point in the cardiac cycle corresponding to a second preset period, a maximum value in a time period (second preset period) in the cardiac cycle corresponding to a first intersection point in the cardiac cycle, a maximum value in a time in a graph (first preset period) in a time period) and a plurality of time in the cardiac cycle corresponding to a first time point in the first time period (7) in the cardiac cycle, a time in the first preset period and a time in the cardiac cycle corresponding to a time point in the first time period (7) and a time in the first time period and the first time period may be shown in the graph may be a graph may be present in the average value, the point d is a point at which the number of occurrences of the section b is largest) and one of the average values of the corresponding pressure ratios in the period from the first occurrence to the last occurrence of the target derivative value in that period (i.e., the fourth preset period) (the period may be referred to as a fifth preset period) in fig. 7, for example. Whereby the target ratio can be obtained.

In some examples, host 30 may select one of the above to obtain the target ratio. Thereby, the pathological change condition of the blood vessel to be detected can be determined.

In some examples, the method for tracking cardiac cycle events using blood pressure according to the first aspect of the present disclosure may include sequentially selecting a predetermined number of pressure ratios from the initial pressure ratios in order of decreasing magnitude, and calculating an average value of the predetermined number of pressure ratios from the selected predetermined number of pressure ratios. In some examples, the target ratio may be an average of the pressure ratios that are sequentially selected a predetermined number in order from decreasing to increasing for the corresponding initial pressure ratio over the selected cardiac cycle. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first change curve and a second change curve, and further obtain a fourth change curve, and may select any cardiac cycle from the fourth change curve to process, where the host 30 may sequentially select a predetermined number (for example, 3, 4, or 5, etc.) of pressure ratios among the pressure ratios corresponding to the cardiac cycle in order from small to large, and the host 30 may calculate an average value of the selected predetermined number of pressure ratios, and use the average value as the target ratio.

In the present disclosure, the pressure within the blood vessel near the proximal side 30a and the pressure within the blood vessel far from the proximal side 30a are measured and a first initial pressure signal and a second initial pressure signal are generated simultaneously a plurality of times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. And sequentially selecting a preset number of pressure ratios from the initial pressure ratios in a descending order, and calculating the average value of the preset number of pressure ratios according to the selected preset number of pressure ratios. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

In some examples, a method of tracking a cardiac cycle event using blood pressure in accordance with a second aspect of the present disclosure may include calculating a ratio of a pressure value of a second initial pressure signal to a pressure value of a first initial pressure signal corresponding to a pressure value of the second initial pressure signal to obtain an initial pressure ratio from the first initial pressure signal and the second initial pressure signal. In some examples, the target ratio may be a minimum of corresponding pressure ratios in diastole within the selected cardiac cycle. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first change curve and a second change curve, so as to obtain a fourth change curve, and may select any cardiac cycle from the fourth change curve to process, where the host 30 may determine a diastole of the cardiac cycle from the selected cardiac cycle, select a minimum pressure ratio from the diastole, and use the minimum pressure ratio as a target ratio.

In the present disclosure, the pressure within the blood vessel near the proximal side 30a and the pressure within the blood vessel far from the proximal side 30a are measured and a first initial pressure signal and a second initial pressure signal are generated simultaneously a plurality of times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. The pressure ratio value within the diastole of the cardiac cycle is obtained from the initial pressure ratio value and the minimum pressure ratio value is selected from the pressure ratio values. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

In some examples, a method of tracking cardiac cycle events using blood pressure in accordance with a third aspect of the present disclosure may include obtaining a pressure ratio value from the initial pressure ratio values that is within a first preset period of the cardiac cycle, and selecting a minimum pressure ratio value from the pressure ratio values. In some examples, the target ratio may be a minimum pressure ratio over a first preset period of the selected cardiac cycle, the first preset period may be a period from a first intersection to a minimum of the first initial pressure signal over the selected cardiac cycle and the first initial pressure signal is at a continuous fall. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first change curve and a second change curve, further obtain a third change curve and a fourth change curve, select any cardiac cycle from the fourth change curve, and process the selected cardiac cycle, and obtain a first intersection point in the cardiac cycle. The host computer 30 may select a minimum pressure ratio from the first intersection point to a minimum value of the first initial pressure signal in the continuous falling period, and may set the minimum pressure ratio as the target ratio.

In the present disclosure, the pressure within the blood vessel near the proximal side 30a and the pressure within the blood vessel far from the proximal side 30a are measured and a first initial pressure signal and a second initial pressure signal are generated simultaneously a plurality of times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. The pressure ratio value is obtained from the initial pressure ratio value for a first predetermined period of the cardiac cycle, and a minimum pressure ratio value is selected from the pressure ratio values. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

In some examples, a method of tracking cardiac cycle events using blood pressure in accordance with a fourth aspect of the present disclosure may include obtaining a pressure ratio value from the initial pressure ratio value that is within a second preset time period of the cardiac cycle, and selecting a pressure ratio value from the pressure ratio values that corresponds to a midpoint time of the second preset time period. In some examples, the target ratio may be a pressure ratio corresponding to a midpoint of a second preset time period within the selected cardiac cycle, which may be a time period from the first intersection to a minimum of the first initial pressure signal within the selected cardiac cycle. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first change curve and a second change curve, further obtain a third change curve and a fourth change curve, select any cardiac cycle from the fourth change curve to process, and obtain a first intersection point in the selected cardiac cycle. The host computer 30 may determine a pressure ratio corresponding to a midpoint of the time period from the first intersection point to the minimum value of the first initial pressure value, and may take the pressure ratio as the target ratio.

In the present disclosure, the pressure within the blood vessel near the proximal side 30a and the pressure within the blood vessel far from the proximal side 30a are measured and a first initial pressure signal and a second initial pressure signal are generated simultaneously a plurality of times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. And obtaining a pressure ratio value in a second preset period of the cardiac cycle from the initial pressure ratio value, and selecting a pressure ratio value corresponding to the midpoint time of the second preset period from the pressure ratio value. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

In some examples, a method of tracking cardiac cycle events using blood pressure in accordance with a fifth aspect of the present disclosure may include obtaining a pressure ratio from the initial pressure ratio that is within a third preset period of the cardiac cycle, and calculating an average of the pressure ratios. In some examples, the target ratio may be an average of pressure ratios over a third preset period of the selected cardiac cycle, which may be a period from the first intersection point to 80% of the cardiac cycle over the selected cardiac cycle. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first change curve and a second change curve, further obtain a third change curve and a fourth change curve, select any cardiac cycle from the fourth change curve to process, and obtain a first intersection point in the selected cardiac cycle. The host 30 may determine the corresponding time at 80% of the cardiac cycle, the host 30 may average the corresponding pressure ratio over the period from the first intersection to 80% of the cardiac cycle, and the average of the pressure ratio may be taken as the target ratio.

In the present disclosure, the pressure within the blood vessel near the proximal side 30a and the pressure within the blood vessel far from the proximal side 30a are measured and a first initial pressure signal and a second initial pressure signal are generated simultaneously a plurality of times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. The pressure ratio is obtained from the initial pressure ratio over a third preset period of the cardiac cycle and an average of the pressure ratios is calculated. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

In some examples, a method of tracking cardiac cycle events using blood pressure in accordance with a sixth aspect of the present disclosure may include obtaining a pressure ratio from the initial pressure ratio that is within a second preset period of the cardiac cycle, and calculating an average of the pressure ratios. In some examples, the target ratio may be an average of pressure ratios over a second preset period of the selected cardiac cycle, which may be a period from a first midpoint time to a second midpoint time within the selected cardiac cycle. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first change curve and a second change curve, further obtain a third change curve and a fourth change curve, select any cardiac cycle from the fourth change curve to process, and obtain a first intersection point in the selected cardiac cycle. The host computer 30 may determine an average value of the pressure ratio over a period from the first intersection point to the minimum value of the first initial pressure value, and take the average value of the pressure ratio as the target ratio.

In the present disclosure, the pressure within the blood vessel near the proximal side 30a and the pressure within the blood vessel far from the proximal side 30a are measured and a first initial pressure signal and a second initial pressure signal are generated simultaneously a plurality of times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. The pressure ratio is obtained from the initial pressure ratio over a second preset period of the cardiac cycle and an average of the pressure ratios is calculated. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

In some examples, a method of tracking cardiac cycle events using blood pressure in accordance with a seventh aspect of the present disclosure may include obtaining a pressure ratio value from the initial pressure ratio value that is within a fourth preset time period of the cardiac cycle, and selecting a pressure ratio value from the pressure ratio values that corresponds to a midpoint time of the fourth preset time period (see point n in fig. 7). In some examples, the target ratio may be a pressure ratio corresponding to a midpoint of a fourth preset time period within the selected cardiac cycle, which may be a time period from a first midpoint time to a second midpoint time within the selected cardiac cycle. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first change curve and a second change curve, and further obtain a fourth change curve and a fifth change curve, and may select any cardiac cycle from the fourth change curve to process, and may obtain a first midpoint time and a second midpoint time in the selected cardiac cycle. The host 30 may determine a midpoint time corresponding to a period from the first midpoint time to the second midpoint time, and determine a pressure ratio corresponding to the midpoint time, and may take the pressure ratio as the target ratio.

In the present disclosure, the pressure within the blood vessel near the proximal side 30a and the pressure within the blood vessel far from the proximal side 30a are measured and a first initial pressure signal and a second initial pressure signal are generated simultaneously a plurality of times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. And obtaining the pressure ratio in the fourth preset period of the cardiac cycle from the initial pressure ratio, and selecting the pressure ratio corresponding to the midpoint time of the fourth preset period from the pressure ratio values. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

In some examples, a method of tracking cardiac cycle events using blood pressure in accordance with the eighth aspect of the present disclosure may include obtaining a pressure ratio from the initial pressure ratio that is within a fifth predetermined period of the cardiac cycle, and calculating an average of the pressure ratios. In some examples, the target ratio may be an average of pressure ratios over a fifth preset time period of the selected cardiac cycle, which may be an average of pressure ratios corresponding to a time period from a first midpoint time to a second midpoint time in the selected cardiac cycle (a fourth preset time period) where the target derivative value in the time period occurs the most frequently in a fifth change curve. Specifically, the host 30 may process the first initial pressure signal and the second initial pressure signal to obtain a first change curve and a second change curve, and further obtain a fourth change curve and a fifth change curve, and may select any cardiac cycle from the fourth change curve to process, and may obtain a first midpoint time and a second midpoint time in the selected cardiac cycle. The host 30 may select, as the target derivative value, the derivative value having the largest number of occurrences in the fifth variation curve from the period from the first midpoint time to the second midpoint time, the host 30 may determine, as the target ratio, the time when the target derivative value first occurs (i.e., the first time) and the time when the target derivative value last occurs (i.e., the second time) in the period from the first midpoint time to the second midpoint time, the host 30 may obtain the average value of the pressure ratios corresponding to the period from the first time to the second time, and may use the average value of the pressure ratios as the target ratio.

In the present disclosure, the pressure within the blood vessel near the proximal side 30a and the pressure within the blood vessel far from the proximal side 30a are measured and a first initial pressure signal and a second initial pressure signal are generated simultaneously a plurality of times during any one cardiac cycle. And calculating the ratio of the pressure value of the second initial pressure signal to the pressure value of the first initial pressure signal corresponding to the pressure value of the second initial pressure signal according to the first initial pressure signal and the second initial pressure signal to obtain an initial pressure ratio. The pressure ratio is obtained from the initial pressure ratio over a fifth preset period of the cardiac cycle and an average of the pressure ratios is calculated. It is thereby possible to provide a method for tracking cardiac circulatory events using blood pressure that does not require the injection of a congestion inducing drug and that is safer and more efficient.

In some examples, if the first initial pressure signal is the first pressure signal and the second initial pressure signal is the second pressure signal, the host 30 may configure the host 30 by selecting one of the above, and may select any cardiac cycle from the waveform chart, and process the first pressure signal and the second pressure signal corresponding to the cardiac cycle to obtain the first target ratio. In other examples, if the first initial pressure signal is the first pressure signal and the second initial pressure signal is the second pressure signal, the host 30 may also select a plurality of cardiac cycles from the waveform chart, perform the above processing on each cardiac cycle, obtain a target ratio (herein referred to as a first target ratio) corresponding to each cardiac cycle, and calculate an average value of the plurality of target ratios according to the plurality of target ratios to obtain a target average value, where the target average value may be used as the first target ratio.

In some examples, the first target ratio may be used as a basis for determining a pathological condition of the blood vessel of the patient, e.g., the first target ratio may be compared to a first preset threshold (or range), and the pathological condition of the blood vessel of the patient may be determined from the result of the comparison. In this case, it is possible to more safely and effectively judge the pathological condition of the blood vessel of the patient without the need to inject a congestion-inducing drug. In some examples, the first preset threshold (or range) may be obtained by measuring intravascular pressure of a normal person (i.e., a condition in which the blood vessel is not diseased).

In the present disclosure, the guide catheter 100 has a first pressure sensor 102 that acquires a first pressure signal near the proximal side 30a in the blood vessel at a first sampling rate, the blood pressure measurement catheter 110 has a second pressure sensor 112 that acquires a second pressure signal at a preset position at the first sampling rate, and at least one side of the second pressure sensor 112 is provided with an X-ray opaque imaging ring. The retraction device 20 is connected to the guide catheter 100 and the blood pressure measuring catheter 110 and controls the retraction of the blood pressure measuring catheter 110 within the blood vessel, the retraction device 20 receiving the first pressure signal and the second pressure signal. The host computer 30 is capable of obtaining an X-ray contrast image of a blood vessel and a real-time image of the blood pressure measurement catheter 110 including a developing ring within the blood vessel, calculating a calculated length of the blood vessel from the width of the developing ring, the X-ray contrast image and the real-time image, and controlling a withdrawal speed of the withdrawal device based on the calculated length, and the host computer 30 is connected with the withdrawal device 20 and receives the first pressure signal and the second pressure signal, thereby obtaining a first target ratio. In this case, the present disclosure can determine the pathological condition of the blood vessel of the patient without the need to inject a congestion-inducing drug.

In some examples, if the first initial pressure signal is the third pressure signal and the second initial pressure signal is the fourth pressure signal, the host 30 may select one of the above to configure the host 30, the host 30 may select a plurality of cardiac cycles from the corresponding waveform diagram to process, and perform the above processing on each cardiac cycle, so as to obtain the second target ratio corresponding to each cardiac cycle. However, examples of the present disclosure are not limited thereto, and in some examples, host 30 may calculate a ratio of each fourth pressure value to a third pressure value corresponding to each fourth pressure value from the third pressure signal and the fourth pressure signal to obtain a plurality of second target ratios. In other examples, during operation of the system 1, the retraction device 20 is configured to control retraction of the blood pressure measurement catheter 110, and the first pressure sensor 102 obtains intravascular pressure from the proximal side 30a at a sampling rate and generates a pressure signal that can be transmitted to the retraction device 102 and further to the host 30 for processing (described below), wherein the first pressure sensor can be non-limiting.

In some examples, host computer 30 may determine a target location within the vessel corresponding to each second target ratio from the obtained plurality of second target ratios, the first image signal, and the second image signal. Specifically, the blood pressure processing apparatus 310 may determine a time corresponding to each of the second target ratios from the obtained plurality of second target ratios, and then determine a target position at which the second pressure sensor 112 is located using the first image signal and the second image signal at the time, and the blood pressure processing apparatus 310 may mark the second target ratio at the target position. The blood pressure processing device 310 may display the X-ray contrast image labeled with the plurality of second target ratios in the image processing device 300 (see the image processing device 300 in fig. 2). In some examples, the second target ratio may be used as a basis for determining a lesion condition of a blood vessel of the patient, and the lesion area of the blood vessel may be determined more specifically based on a comparison result of the second target ratio of each target position on the image and the first preset threshold (or range), so that the size of the portion to be implanted with the stent may be determined more specifically.

However, examples of the present disclosure are not limited thereto, and in some examples, the retraction device 20 is configured to control retraction of the blood pressure measurement catheter 110 when the system 1 is in operation, and the second pressure sensor 112 may measure the intravascular pressure distal the proximal side 30a and generate a third pressure signal, which may be received by the host 30. The host 30 may determine each cardiac cycle included in the third pressure signal according to the third pressure signal, further determine a pressure value corresponding to a diastole end of each cardiac cycle, and determine a position corresponding to each pressure value in the X-ray contrast image based on the X-ray contrast image and the real-time image, further determine a specific lesion condition of a blood vessel of the patient according to the pressure values corresponding to a plurality of positions in the X-ray contrast image, and further more specifically determine a size of a portion to be implanted into the stent.

In other examples, during operation of the system 1, the retraction device 20 is configured to control retraction of the blood pressure measurement catheter 110, and the second pressure sensor 112 may measure the pressure within the blood vessel distal from the proximal side 30a and generate a third pressure signal, and the external instrument may simultaneously obtain an electrocardiogram of the patient, and the host 30 may receive the third pressure signal. According to the electrocardiogram and the third pressure signals, the corresponding pressure value of the diastolic end of each cardiac cycle in the third pressure signals can be determined, the host computer 30 determines the corresponding position of each pressure value in the X-ray contrast image based on the X-ray contrast image and the real-time image, and then the specific pathological change condition of the blood vessel of the patient can be determined according to the pressure values corresponding to a plurality of positions in the X-ray contrast image, and further the size of the part to be implanted with the stent can be more specifically determined.

In some examples, pressure measurements may be made with blood pressure measurement device 10 for each coronary artery in an X-ray contrast image and processed with host computer 30, whereby specific lesions of each coronary artery may be determined.

While the disclosure has been described in detail in connection with the drawings and embodiments, it should be understood that the foregoing description is not intended to limit the disclosure in any way. Modifications and variations of the present disclosure may be made as desired by those skilled in the art without departing from the true spirit and scope of the disclosure, and such modifications and variations fall within the scope of the disclosure.

Claims

1. A host computer for processing pressure signals, characterized in that,

the host is configured to receive a first initial pressure signal and a second initial pressure signal, wherein the first initial pressure signal is generated by measuring the pressure of the side of the blood vessel near the proximal end in any cardiac cycle at a first sampling rate, and the second initial pressure signal is generated by measuring the pressure of the side of the blood vessel far from the proximal end at a second sampling rate, and the first sampling rate is in the range of 30Hz to 1.5KHz, and the second sampling rate is in the range of 30Hz to 1.5KHz;

the host is further configured to calculate a ratio of a pressure value of the second initial pressure signal to a pressure value of the first initial pressure signal corresponding to a pressure value of the second initial pressure signal to obtain an initial pressure ratio based on the first initial pressure signal and the second initial pressure signal, and

Obtaining a pressure ratio value from said initial pressure ratio value that is within a first preset period of said cardiac cycle, and selecting a minimum pressure ratio value from said pressure ratio values,

wherein the average value of the pressure values of the first initial pressure signal is obtained according to the first initial pressure signal, a first intersection point is obtained according to the first initial pressure signal and the average value, the first preset period is the period from the first intersection point to the minimum value of the first initial pressure signal and the first initial pressure signal is in continuous descending,

the minimum pressure ratio is used for comparing with a first preset threshold value to judge the pathological condition of the blood vessel.

2. A host computer for processing pressure signals, characterized in that,

Obtaining a pressure ratio value located in a second preset period of the cardiac cycle from the initial pressure ratio value, selecting a pressure ratio value corresponding to a midpoint time of the second preset period from the pressure ratio values,

wherein the average value of the pressure values of the first initial pressure signal is obtained according to the first initial pressure signal, the first intersection point is obtained according to the first initial pressure signal and the average value, the second preset period is the period from the first intersection point to the minimum value of the first initial pressure signal,

the pressure ratio corresponding to the midpoint time of the second preset period is used for comparing with the first preset threshold value to judge the pathological change condition of the blood vessel.

3. A host computer for processing pressure signals, characterized in that,

obtaining a pressure ratio from said initial pressure ratio, which is located within a third preset period of said cardiac cycle, and calculating an average of said pressure ratios,

wherein a mean value of pressure values of the first initial pressure signal is obtained from the first initial pressure signal, a first intersection is obtained from the first initial pressure signal and the mean value, the third preset period is a period from the first intersection to 80% of the cardiac cycle,

the average value is used for comparing with a first preset threshold value to judge the pathological condition of the blood vessel.

4. A host computer for processing pressure signals, characterized in that,

obtaining a pressure ratio from said initial pressure ratio, which is located within a second preset period of said cardiac cycle, and calculating an average of said pressure ratios,

5. A host computer for processing pressure signals, characterized in that,

obtaining a pressure ratio value in a fourth preset period of the cardiac cycle from the initial pressure ratio value, selecting a pressure ratio value corresponding to the midpoint time of the fourth preset period from the pressure ratio values,

wherein the derivative of the second initial pressure signal relative to time is obtained according to the second initial pressure signal, the first midpoint time and the second midpoint time are obtained according to the second initial pressure signal and the derivative, the fourth preset period is the period from the first midpoint time to the second midpoint time,

and the pressure ratio corresponding to the midpoint time of the fourth preset period is used for comparing with a first preset threshold value to judge the pathological change condition of the blood vessel.

6. A host computer for processing pressure signals, characterized in that,

obtaining a pressure ratio from said initial pressure ratio, which is within a fifth preset period of said cardiac cycle, and calculating an average value of said pressure ratios,

wherein the fifth preset period is a target derivative value with the largest occurrence number of the derivative value of the second initial pressure signal relative to time in a fourth preset period and the target derivative value in the fourth preset period occurs from the first occurrence to the last occurrence, the derivative of the second initial pressure signal relative to time is obtained according to the second initial pressure signal, a first midpoint time and a second midpoint time are obtained according to the second initial pressure signal and the derivative, the fourth preset period is a period from the first midpoint time to the second midpoint time,