Cardiac output determination method, device and equipment

Abstract

The invention discloses a cardiac output determination method, device and equipment, and belongs to the technical field of medical treatment. The method comprises the following steps: determining the content of a signal marker of an input target object; the method comprises the following steps: detecting a signal marker in the blood of a target object through an ultrasonic detection device which is arranged at at least one preset part in advance to obtain a time-intensity curve of the signal marker; and determining the discontinuous cardiac output of the target object based on the content of the signal marker of the input target object, the curve area of the time-intensity curve of the signal marker and the concentration of the signal marker. The method does not need to depend on the operation level and experience of an operator, and safe, stable and accurate cardiac output detection can be achieved.

Description

Technical Field

[0001] This application relates to the field of medical technology, specifically to methods, apparatus, and equipment for determining cardiac output. Background Technology

[0002] Cardiac output (CO) is a core indicator for clinical assessment of circulatory function and cardiac pumping status, and it has important value in intensive care, cardiovascular disease treatment, and surgical anesthesia management.

[0003] Relevant methods for measuring cardiac output mainly include non-invasive echocardiography. This involves measuring the velocity-time integral (VTI) and cross-sectional area of ​​the left ventricular outflow tract (LVOT) via transthoracic or transesophageal echocardiography to calculate stroke volume and thus estimate cardiac output. However, this method heavily relies on the operator's skill and experience; image acquisition and parameter measurement are highly subjective, which can easily affect the accuracy and repeatability of the measurement results. Summary of the Invention

[0004] The purpose of this application is to overcome the shortcomings of the prior art and provide a method, apparatus and equipment for determining cardiac output that does not rely on the operator's skill level and experience, and can achieve safe, stable and accurate cardiac output detection.

[0005] To achieve the above objectives, this application adopts the following technical solution: In a first aspect, this application provides a method for determining intermittent cardiac output. According to an embodiment of this application, the method includes: determining the content of a signal marker in an input target object; detecting the signal marker in the blood of the target object using an ultrasound detection device placed at least one predetermined site in advance, and obtaining a time-intensity curve of the signal marker; and determining the intermittent cardiac output of the target object based on the content of the signal marker in the input target object, the area under the time-intensity curve of the signal marker, and the concentration of the signal marker.

[0006] In an exemplary embodiment, the discontinuous cardiac output of the target object is determined based on the formula shown in Equation 1). Equation 1); Where CO represents the intermittent cardiac output of the target object, k1 represents the calibration coefficient, C0 is the concentration of the signal marker, and V inj This indicates the content of signal markers in the input target object. This represents the area under the time-intensity curve of the signal marker during the time interval t1-t2.

[0007] In an exemplary embodiment, the predetermined sites include: the carotid artery, the left ventricular outflow tract, the renal artery, and the distal digital artery.

[0008] In an exemplary embodiment, the signal marker is selected from ultrasound contrast agents.

[0009] In an exemplary embodiment, the ultrasonic testing device is selected from an ultrasonic probe.

[0010] Secondly, this application proposes a method for determining continuous cardiac output. According to an embodiment of this application, the method includes: determining the blood flow waveform at at least one predetermined site of a subject to be examined to obtain a blood flow velocity-time curve; determining the continuous cardiac output of the subject to be examined based on the area under the blood flow velocity-time curve, the vascular radius of the subject to be examined, the heart rate of the subject to be examined, and a first intermittent cardiac output; wherein the first intermittent cardiac output is obtained by the method described in any example of the first aspect.

[0011] In an exemplary embodiment, the discontinuous cardiac output of the target object is determined based on the formula shown in Equation 2). Equation 2); Where CCO represents the continuous cardiac output of the subject; k2 represents the correction coefficient; HR represents the heart rate of the subject; VTI represents the area under the curve of the blood flow velocity-time curve; and r is the radius of the blood vessel of the subject.

[0012] In an exemplary embodiment, the correction coefficient k2 is the ratio of the first intermittent cardiac output to the second intermittent cardiac output within a predetermined time period; wherein, the second intermittent cardiac output is determined by the area of ​​the blood flow velocity-time curve, the vascular radius of the subject under test, and the heart rate of the subject under test within the predetermined time period.

[0013] Thirdly, this application proposes an intermittent cardiac output determination device. According to an embodiment of this application, the device includes: a signal marker content determination module for determining the signal marker content of an input target object; a detection module for detecting the signal marker in the blood of the target object using an ultrasound detection device placed at least one predetermined site in advance, and obtaining a time-intensity curve of the signal marker; and an intermittent cardiac output calculation module for determining the intermittent cardiac output of the target object based on the signal marker content of the input target object, the area under the time-intensity curve of the signal marker, and the concentration of the signal marker.

[0014] Fourthly, this application proposes a continuous cardiac output (CPO) determination device. According to an embodiment of this application, the device includes: a blood flow waveform determination module, used to determine the blood flow waveform at at least one predetermined location of a subject under examination, obtaining a blood flow velocity-time curve; and a continuous cardiac output (CPO) calculation module, used to determine the continuous cardiac output of the subject under examination based on the area under the blood flow velocity-time curve, the vascular radius of the subject under examination, the heart rate of the subject under examination, and a first intermittent cardiac output; wherein the first intermittent cardiac output is obtained by the method described in any example of the first aspect.

[0015] Fifthly, this application proposes an electronic device. According to an embodiment of this application, the electronic device includes: a processor and a memory; the memory is used to store a computer program; the processor is used to execute the computer program to implement the intermittent cardiac output determination method as described in the first aspect of this application or the continuous cardiac output determination method as described in the second aspect.

[0016] Sixthly, this application proposes a computer-readable storage medium. According to embodiments of this application, the computer-readable storage medium stores computer instructions or programs that, when executed on a computer, cause the intermittent cardiac output determination method as described in the first aspect or the continuous cardiac output determination method as described in the second aspect of this application to be performed.

[0017] In a seventh aspect, this application proposes a computer program product. According to an embodiment of this application, the computer program product includes computer instructions that, when some or all of the computer instructions are executed on a computer, cause the intermittent cardiac output determination method as described in the first aspect or the continuous cardiac output determination method as described in the second aspect of this application to be performed.

[0018] The technical solution of this application embodiment introduces a quantifiable signal marker into the blood of a target subject and uses a pre-placed ultrasound detection device to acquire its time-intensity curve (TIC) over time. Intermittent cardiac output is directly calculated based on the input amount, the area under the TIC curve, and the marker concentration, without relying on manual intervention. Compared with existing cardiac output measurement methods based on LVOT VTI, this method eliminates the need for human skill and experience, significantly reducing the impact of operator subjectivity on measurement results, improving the accuracy and repeatability of cardiac output measurement, and making cardiac output acquisition more efficient, objective, and stable. Attached Figure Description

[0019] The above and / or additional aspects and advantages of this application will become apparent and readily understood from the description of the embodiments taken in conjunction with the following drawings, in which: Figure 1A schematic flowchart of the method for determining intermittent cardiac output provided in an embodiment of this application; Figure 2 This is a schematic diagram illustrating the principle of obtaining cardiac output via contrast agent dilution in an embodiment of this application; wherein, A represents the contrast agent entering the circulation via a vein; B represents the contrast agent mixing with the blood flow via blood circulation; and C represents the contrast agent concentration in the downstream artery (converted to echo intensity by ultrasound measurement). Figure 3 A schematic diagram of the time-intensity curve of ultrasound contrast imaging provided in this application embodiment; wherein t1 is the injection time, t2 is the elimination time, TTP is the peak time, RT is the rise time, FT is the fall time, and AUC is the area under the curve; Figure 4 This is a schematic flowchart of the continuous output quantity determination method provided in the embodiments of this application; Figure 5 A schematic diagram of a multi-site tissue blood flow estimation simulation provided for embodiments of this application; Figure 6 This is a schematic diagram of blood flow waveforms under Doppler ultrasound of the left ventricular outflow tract provided in an embodiment of this application. Figure 7 A schematic diagram of the intermittent cardiac output determination device provided in the embodiments of this application; Figure 8 This is a schematic diagram illustrating the determination of continuous cardiac output volume provided in an embodiment of this application; Figure 9 A schematic diagram of an electronic device provided in an embodiment of this application. Detailed Implementation

[0020] The embodiments of this application are described in detail below. The embodiments described below are exemplary and are only used to explain this application, and should not be construed as limiting this application.

[0021] It should be noted that the terms "first," "second," etc., in the specification, claims, and accompanying drawings of this application are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. It should be understood that such data can be interchanged where appropriate so that the embodiments of this application described herein can be implemented in sequences other than those illustrated or described herein. In embodiments of this application, "B corresponding to A" means that B is associated with A. In one implementation, B can be determined based on A. However, it should also be understood that determining B based on A does not mean determining B solely based on A; B can also be determined based on A and / or other information. Furthermore, the terms "comprising" and "having," and any variations thereof, are intended to cover non-exclusive inclusion. For example, a process, method, system, product, or server that comprises a series of steps or units is not necessarily limited to those steps or units explicitly listed, but may include other steps or units not explicitly listed or inherent to these processes, methods, products, or devices. In the description of this application, unless otherwise stated, "a plurality of" means two or more.

[0022] In the embodiments of this application, the terms "module" or "unit" refer to a computer program or part of a computer program that has a predetermined function and works with other related parts to achieve a predetermined goal, and can be implemented wholly or partially using software, hardware (such as processing circuitry or memory), or a combination thereof. Similarly, a processor (or multiple processors or memory) can be used to implement one or more modules or units. Furthermore, each module or unit can be part of an overall module or unit that includes the functionality of that module or unit.

[0023] Before introducing the technical solution of this application, the relevant knowledge of this application will be introduced below: In the embodiments of this application, "cardiac output (CO)" refers to the total amount of blood ejected by the heart per unit time, which is an important parameter for evaluating circulatory function and the heart's pumping ability.

[0024] In the embodiments of this application, "intermittent cardiac output" refers to the cardiac output calculated based on the detection results over a specific time period. Its measurement is intermittent, which is different from real-time and continuous monitoring.

[0025] In the embodiments of this application, "continuous cardiac output" refers to the cardiac output obtained by continuous monitoring and calculation of hemodynamic signals over a relatively long period of time, which can dynamically reflect the trend of blood flow changes compared to intermittent cardiac output.

[0026] In this embodiment, "signal marker" refers to a tracer substance used for hemodynamic measurement, which is distributed in the blood during circulation and can be identified and imaged by an ultrasound detection device. In a preferred embodiment, the signal marker is an ultrasound contrast agent.

[0027] In the embodiments of this application, "the content of signal markers in the target object" refers to the absolute dose of signal markers injected into the body of the object being tested, usually expressed by volume.

[0028] In the embodiments of this application, "signal marker concentration" refers to the concentration value of the signal marker at the detection site in the blood circulation of the target object. This concentration can be estimated by combining the input volume and blood dilution.

[0029] In the embodiments of this application, the "time-intensity curve" refers to the signal intensity curve that changes over time when ultrasound imaging is performed on signal markers in blood at the target detection site (i.e., one of the predetermined sites). The area of ​​the curve reflects the total amount of signal markers passing through the detection cross section per unit time.

[0030] In the embodiments of this application, "area of ​​curve" refers to the integral value under the time-intensity curve within a selected time interval (t1-t2 or injection-clearance), which can characterize the amount of signal markers carried by the blood during that time period.

[0031] In the embodiments of this application, the "blood flow velocity-time curve" refers to the value obtained by measuring blood flow velocity using ultrasound Doppler and integrating the velocity curve over one cardiac cycle, which is used to reflect the length of the blood travel through the detection section over one cardiac cycle.

[0032] In the embodiments of this application, "vascular radius (r)" refers to the radius of the blood vessel at the target detection site, which is used to calculate the cross-sectional area of ​​the lumen of the blood vessel or the ventricular outflow tract.

[0033] In the embodiments of this application, "heart rate (HR)" refers to the number of heartbeats per unit time (usually 1 minute) of the target object. Heart rate is combined with stroke volume to calculate cardiac output.

[0034] In the embodiments of this application, "calibration coefficient (k1)" refers to an empirical or experimental correction factor introduced during the intermittent cardiac output measurement process to compensate for individual differences and equipment measurement errors.

[0035] In the embodiments of this application, "correction coefficient (k2)" refers to the proportional factor used to correct the continuous calculation result by the intermittent cardiac output result during the continuous cardiac output measurement process. It is usually the ratio of the first intermittent cardiac output to the second intermittent cardiac output within a predetermined time period.

[0036] In the embodiments of this application, "predetermined site" refers to the location of a blood vessel used to place an ultrasound detection device or collect blood flow signals, including but not limited to the carotid artery, left ventricular outflow tract (LVOT), renal artery and distal digital artery.

[0037] In the embodiments of this application, "ultrasound detection device" refers to a device that can detect signal markers or blood flow velocity based on ultrasound principles, preferably a clinically commonly used ultrasound probe, which can be a transthoracic, transesophageal, or vascular local detection method.

[0038] The technical problems to be solved and the inventive concept to be presented in the embodiments of this application will be described below: As mentioned earlier, relevant cardiac output measurement methods mainly include non-invasive echocardiography. Other methods include thermodilution and pulse contour analysis. Thermodulation methods are typically performed intermittently using a pulmonary artery catheter (PAC) or a PiCCO system. The PAC method has been widely used and considered a clinical reference standard due to its accurate reflection of cardiac output (CO) and stroke volume (SV). However, PAC procedures require the insertion of a pulmonary artery catheter, a highly invasive procedure with risks of infection, arrhythmias, and pulmonary artery injury, thus limiting its clinical application. As an alternative, the PiCCO system is more widely used clinically. Its thermodilution module achieves measurement through rapid central venous injection of hypothermic saline, avoiding the need for pulmonary artery catheter insertion. However, this method still requires multiple rapid injections of hypothermic fluid, potentially leading to hemodynamic instability or arrhythmias. Furthermore, it demands precise control over injection dosage, rate, and fluid temperature; non-compliance can cause deviations in the thermodilution curve, affecting measurement accuracy. In addition, the PiCCO system still requires a central venous catheter, posing risks of catheter-related infections and bleeding.

[0039] Pulse contour analysis, based on morphological analysis of arterial pressure waveforms and combined with parameters such as vascular compliance and peripheral resistance, enables continuous estimation of cardiac output. This method provides real-time monitoring, but its measurement accuracy depends on the peripheral vascular mechanics, typically requiring initial calibration and recalibration when hemodynamic conditions change. Because accurate real-time acquisition of vascular mechanics parameters is difficult in clinical practice, the calibration time point is uncertain, potentially affecting the stability and reliability of the measurement results.

[0040] To address the aforementioned issues, this application proposes a method for determining cardiac output. By determining the content of a signal marker in the target subject, such as through peripheral intravenous injection of ultrasound contrast agent, reliance on pulmonary artery catheters is avoided, reducing invasive risks. Furthermore, using an ultrasound detection device placed at least one predetermined site, a time-intensity curve (TIC) of the signal marker in the target subject's blood is acquired. This curve objectively reflects the dynamic process of the contrast agent in blood flow, thus avoiding the subjective biases of traditional ultrasound measurements dependent on operator input. Then, based on the input content of the signal marker, the area under the time-intensity curve, and the signal marker concentration, the intermittent cardiac output of the target subject is calculated. Through these operations, this embodiment enables intermittent cardiac output measurement without the need for pulmonary artery catheters and complex procedures, effectively reducing the risks of infection, arrhythmia, and hemodynamic instability caused by catheter insertion or rapid injection of ice-cold saline. Simultaneously, utilizing the objective parameters of the TIC curve reduces errors caused by subjectivity in image acquisition and measurement, improving measurement accuracy and repeatability. Therefore, the technical solution of this application has high safety, simplicity and reliability, and can provide a more feasible means of assessing cardiac output for intensive care, perioperative management and diagnosis and treatment of acute and critical illnesses.

[0041] Method for determining intermittent cardiac output Firstly, this application provides a method for determining intermittent cardiac output. (Reference) Figure 1 The method includes: S110, Determine the content of signal markers in the input target object; In an exemplary embodiment, reference is made to Figure 2 The signal marker can be a tracer substance that can be identified by an ultrasound imaging detection device. In a specific embodiment, it can be an ultrasound contrast agent, such as a microbubble contrast agent containing a phospholipid shell or a protein shell. Contrast-Enhanced Ultrasound (CEUS) is a technique that enhances ultrasound images by intravenously injecting a contrast agent containing microbubbles to display blood flow and tissue structures. Its advantages include: 1) Small injection volume of contrast agent, generally only 1-2 ml is needed to achieve a significant imaging enhancement effect; 2) The main component of ultrasound contrast agent is microbubbles encapsulating inert gas, whose diameter is usually smaller than that of red blood cells. It can be excreted from the body through pulmonary circulation, while the outer shell component can be metabolized in the liver. Therefore, it has the advantages of good biological inertness, no nephrotoxicity, rapid metabolism, and low risk of allergies, resulting in fewer side effects and high safety, making it suitable for a variety of patient groups; 3) Ultrasound contrast agents can be administered via peripheral intravenous injection, which is non-invasive and has good clinical applicability, making it convenient for use in different clinical scenarios.

[0042] In an exemplary embodiment, the signal marker may be input via peripheral vein or central vein injection, preferably via peripheral vein injection, to reduce invasive procedures on the target object.

[0043] In practice, a predetermined dose of the signal marker can be injected into the target's circulatory system by controlling a syringe or infusion pump to form a detectable concentration change curve. The input content can be determined by parameters such as the injection volume, concentration, and rate of the contrast agent. For example, in one embodiment, 1-2 mL of ultrasound contrast agent solution can be rapidly injected over 1-2 seconds, supplemented by a 5-10 mL saline bolus to ensure rapid entry of the contrast agent into the circulatory system.

[0044] The above method can be used to obtain the initial input content of signal markers in the target object's blood circulation system.

[0045] S120, using an ultrasound detection device placed at least one predetermined site, the signal markers in the blood of the target object are detected, and the time-intensity curve of the signal markers is obtained; In an exemplary embodiment, the ultrasound detection device can be a conventional ultrasound probe, including but not limited to a phased array probe, a convex array probe, or a linear array probe, preferably a probe with contrast imaging capabilities. The predetermined site can be a blood vessel or cardiac outflow tract that can represent hemodynamic characteristics, such as the carotid artery, left ventricular outflow tract, renal artery, or distal digital artery. By placing the probe at the above-mentioned site and activating the contrast imaging mode, the intensity of the echo signal generated by changes in the concentration of signal markers in the blood flow can be acquired in real time.

[0046] In practice, after the signal marker enters the bloodstream, it causes a dynamic change in the intensity of the ultrasound echo at the probe's imaging plane over time. (Reference) Figure 3 The system can perform grayscale quantification or intensity value extraction on the acquired ultrasound images to obtain a time-intensity curve (TIC) showing the change in signal intensity over time within the target area. The vertical axis of this curve represents signal intensity (usually expressed in arbitrary units of au), and the horizontal axis represents time (usually in seconds), reflecting the distribution and clearance process of signal markers in the blood.

[0047] S130, based on the signal marker content of the input target object, the area under the time-intensity curve of the signal marker, and the concentration of the signal marker, determine the intermittent cardiac output of the target object.

[0048] In an exemplary embodiment, the input content of the signal marker can be directly determined by the injection dose, and the area under the curve (AUC) of the time-intensity curve of the signal marker is obtained by integrating the TIC curve obtained during the injection-to-clearance period. The concentration of the signal marker can be obtained by a preset contrast agent property.

[0049] In an exemplary specific embodiment, the discontinuous cardiac output of the target object is determined based on the formula shown in Equation 1). Equation 1); Where CO represents the intermittent cardiac output of the target object, k1 represents the calibration coefficient, C0 is the concentration of the signal marker, and V inj This indicates the content of signal markers in the input target object. This represents the area under the time-intensity curve of the signal marker during the time interval t1-t2.

[0050] The above calculation method avoids the need for operator-dependent flow rate parameter measurement and directly utilizes the dynamic distribution characteristics of signal markers to estimate cardiac output, thereby improving the accuracy and repeatability of the measurement.

[0051] In summary, the proposed method employs a low-dose, short-time injection strategy for signal markers, which can significantly reduce the risk of hemodynamic instability caused by rapid infusion of large amounts of diluent in traditional methods. This reduces the occurrence of complications such as hypotension and arrhythmia, making it particularly suitable for critically ill or vulnerable patients and improving the safety and tolerability of the overall monitoring process.

[0052] Secondly, the proposed protocol offers high convenience in clinical operation. Due to the small injection volume and short operation time, the measurement process is less dependent on the operator's skill, avoiding measurement failures or data deviations caused by operational errors, thus improving the accuracy and repeatability of test results. Simultaneously, this protocol allows for contrast agent injection only through peripheral blood vessels, reducing complications such as infection and bleeding associated with invasive procedures, and shortening the monitoring process, thereby improving testing efficiency.

[0053] Furthermore, this proposed protocol supports continuous circulatory monitoring, reflecting not only macrocirculatory blood flow but also comprehensive assessment of perfusion in multiple sites and the microcirculation, thus providing clinicians with more comprehensive hemodynamic information. This makes the protocol particularly suitable for clinical scenarios with high requirements for tissue perfusion assessment, such as septic shock, severe trauma, and perioperative management, helping to guide physicians in making individualized treatment decisions and improving the scientific accuracy of prognostic assessments.

[0054] Method for determining continuous output Secondly, this application proposes a method for determining continuous cardiac output, referring to... Figure 4 The method includes: S410, determine the blood flow waveform at at least one predetermined site of the object to be examined, and obtain the blood flow velocity-time curve; In an exemplary embodiment, an ultrasound Doppler blood flow detection device can be used to image and measure the target blood vessel, selecting one or more detection sites related to cardiac output calculation, such as the carotid artery, left ventricular outflow tract, renal artery, or distal digital artery location, etc. Figure 5 During the measurement process, the system continuously acquires blood flow signals to obtain raw data on the change of blood flow velocity over time. Then, based on this raw data, filtering, denoising, and baseline correction are performed to ensure that the obtained signal waveform has a high signal-to-noise ratio and stability.

[0055] refer to Figure 6 Through the above processing, a complete velocity-time curve (VTC) can be extracted, which can accurately reflect the hemodynamic characteristics of the target vessel in one or more cardiac cycles.

[0056] In an exemplary embodiment, the present application embodiments are capable of continuously outputting cardiac output estimates, which is applicable to clinical scenarios with rapidly changing hemodynamics.

[0057] In an exemplary embodiment, the present application embodiments can use a multi-probe or multi-channel ultrasound system to simultaneously acquire blood flow parameters of multiple body parts (such as the carotid artery, left ventricular outflow tract, renal artery, or distal digital artery, etc.), thereby estimating the tissue flow status of the corresponding area, realizing joint monitoring of macrocirculation and microcirculation, and improving the comprehensiveness and specificity of diagnosis.

[0058] S420, based on the area under the blood flow velocity-time curve, the vascular radius of the subject under test, the heart rate of the subject under test, and the first intermittent cardiac output, the continuous cardiac output of the subject under test is determined; wherein, the first intermittent cardiac output is obtained by the aforementioned method.

[0059] In an exemplary embodiment, the blood flow velocity-time curve is integrated to obtain the velocity-time integral (VTI) per unit cardiac cycle. Combined with a pre-measured vessel radius, the vessel cross-sectional area can be calculated, and then multiplied by the VTI to obtain the stroke volume of that vessel in one cardiac cycle. Subsequently, the stroke volume is multiplied by the heart rate of the subject to obtain the cardiac output measured by ultrasound.

[0060] In an exemplary embodiment, the discontinuous cardiac output of the target object is determined based on the formula shown in Equation 2). Equation 2); Where CCO represents the continuous cardiac output of the subject; k2 represents the correction coefficient; HR represents the heart rate of the subject; VTI represents the area under the curve of the blood flow velocity-time curve; and r is the radius of the blood vessel of the subject.

[0061] To further improve the accuracy of continuous measurements, this application introduces a first intermittent cardiac output as a reference correction value. This first intermittent cardiac output can be obtained through thermodilution or other standard blood flow monitoring methods. During continuous monitoring, the system corrects for deviations in the ultrasound measurement results based on this intermittent reference value to eliminate cumulative errors caused by factors such as detection angle, vascular elasticity, or signal drift. Thus, while ensuring long-term stability, it is possible to dynamically determine the continuous cardiac output of the subject under examination.

[0062] In an exemplary embodiment, the correction coefficient k2 is the ratio of the first intermittent cardiac output to the second intermittent cardiac output within a predetermined time period; wherein, the second intermittent cardiac output is determined by the area of ​​the blood flow velocity-time curve, the vascular radius of the subject under test, and the heart rate of the subject under test within the predetermined time period.

[0063] Intermittent core output determination device Thirdly, this application proposes a device for determining intermittent cardiac output. (Reference) Figure 7 The device includes: a signal marker content determination module 710, a detection module 720, and an intermittent cardiac output calculation module 730.

[0064] The signal marker content determination module 710 is used to determine the signal marker content of the input target object; the detection module 720 is used to detect the signal marker in the blood of the target object by using an ultrasound detection device placed at least one predetermined site in advance, and obtain the time-intensity curve of the signal marker; the intermittent cardiac output calculation module 730 is used to determine the intermittent cardiac output of the target object based on the signal marker content of the input target object, the area of ​​the time-intensity curve of the signal marker, and the concentration of the signal marker.

[0065] In an exemplary embodiment, the discontinuous cardiac output of the target object is determined based on the formula shown in Equation 1). Equation 1); Where CO represents the intermittent cardiac output of the target object, k1 represents the calibration coefficient, C0 is the concentration of the signal marker, and V injThis indicates the content of signal markers in the input target object. This represents the area under the time-intensity curve of the signal marker during the time interval t1-t2.

[0066] In an exemplary embodiment, the predetermined sites include: the carotid artery, the left ventricular outflow tract, the renal artery, and the distal digital artery.

[0067] In an exemplary embodiment, the signal marker is selected from ultrasound contrast agents.

[0068] In an exemplary embodiment, the ultrasonic testing device is selected from an ultrasonic probe.

[0069] It should be understood that the device embodiments and method embodiments can correspond to each other, and similar descriptions can be referred to the method embodiments. To avoid repetition, they will not be repeated here. Specifically, this device can execute the corresponding method embodiments described above, and the foregoing and other operations and / or functions of each module in the device are respectively for implementing the corresponding processes in the above methods. For the sake of brevity, they will not be repeated here.

[0070] The apparatus of this application embodiment has been described above from the perspective of functional modules in conjunction with the accompanying drawings. It should be understood that this functional module can be implemented in hardware, in software instructions, or in a combination of hardware and software modules. Specifically, the steps of the method embodiments in this application can be completed by integrated logic circuits in the processor's hardware and / or by software instructions. The steps of the method disclosed in this application embodiment can be directly embodied as being executed by a hardware decoding processor, or by a combination of hardware and software modules in the decoding processor. Optionally, the software module can reside in a mature storage medium in the art, such as random access memory, flash memory, read-only memory, programmable read-only memory, electrically erasable programmable memory, registers, etc. This storage medium is located in memory, and the processor reads information from the memory and, in conjunction with its hardware, completes the steps in the above method embodiments.

[0071] Continuous output determination device Fourthly, this application proposes a continuous output quantity determination device, referring to... Figure 8 The device includes a blood flow waveform determination module 810 and a continuous cardiac output calculation module 820.

[0072] The blood flow waveform determination module 810 is used to determine the blood flow waveform at at least one predetermined part of the subject under examination to obtain a blood flow velocity-time curve; the continuous cardiac output calculation module 820 is used to determine the continuous cardiac output of the subject under examination based on the area of ​​the blood flow velocity-time curve, the vascular radius of the subject under examination, the heart rate of the subject under examination, and a first intermittent cardiac output; wherein the first intermittent cardiac output is obtained by the method described in the first aspect.

[0073] In an exemplary embodiment, the discontinuous cardiac output of the target object is determined based on the formula shown in Equation 2). Equation 2); Where CCO represents the continuous cardiac output of the subject; k2 represents the correction coefficient; HR represents the heart rate of the subject; VTI represents the area under the curve of the blood flow velocity-time curve; and r is the radius of the blood vessel of the subject.

[0074] In an exemplary embodiment, the correction coefficient k2 is the ratio of the first intermittent cardiac output to the second intermittent cardiac output within a predetermined time period; wherein, the second intermittent cardiac output is determined by the area of ​​the blood flow velocity-time curve, the vascular radius of the subject under test, and the heart rate of the subject under test within the predetermined time period.

[0075] It should be understood that the device embodiments and method embodiments can correspond to each other, and similar descriptions can be referred to the method embodiments. To avoid repetition, they will not be repeated here. Specifically, this device can execute the corresponding method embodiments described above, and the foregoing and other operations and / or functions of each module in the device are respectively for implementing the corresponding processes in the above methods. For the sake of brevity, they will not be repeated here.

[0076] The apparatus of this application embodiment has been described above from the perspective of functional modules in conjunction with the accompanying drawings. It should be understood that this functional module can be implemented in hardware, in software instructions, or in a combination of hardware and software modules. Specifically, the steps of the method embodiments in this application can be completed by integrated logic circuits in the processor's hardware and / or by software instructions. The steps of the method disclosed in this application embodiment can be directly embodied as being executed by a hardware decoding processor, or by a combination of hardware and software modules in the decoding processor. Optionally, the software module can reside in a mature storage medium in the art, such as random access memory, flash memory, read-only memory, programmable read-only memory, electrically erasable programmable memory, registers, etc. This storage medium is located in memory, and the processor reads information from the memory and, in conjunction with its hardware, completes the steps in the above method embodiments.

[0077] Electronic equipment, media, products Figure 9 This is a schematic block diagram of an electronic device 900 provided in an embodiment of this application. The electronic device 900 may be the aforementioned training device or execution device, but is not limited thereto. Figure 9 As shown, the electronic device 900 may include: The system includes a memory 910 and a processor 920. The memory 910 stores a computer program 930 and transfers the computer program 930 to the processor 920. In other words, the processor 920 can retrieve and run the computer program 930 from the memory 910 to implement the methods described in the embodiments of this application.

[0078] For example, the processor 920 can be used to execute the steps in the above method according to the instructions in the computer program 930.

[0079] In some embodiments of this application, the processor 920 may include, but is not limited to: General-purpose processors, digital signal processors (DSPs), application-specific integrated circuits (ASICs), field-programmable gate arrays (FPGAs), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc.

[0080] In some embodiments of this application, the memory 910 includes, but is not limited to: Volatile memory and / or non-volatile memory. Non-volatile memory can be read-only memory (ROM), programmable read-only memory (PROM), erasable programmable read-only memory (EPROM), electrically erasable programmable read-only memory (EEPROM), or flash memory. Volatile memory can be random access memory (RAM), used as an external cache. By way of example, but not limitation, many forms of RAM are available, such as Static RAM (SRAM), Dynamic RAM (DRAM), Synchronous DRAM (SDRAM), Double Data Rate SDRAM (DDR SDRAM), Enhanced SDRAM (ESDRAM), Synchronous Link DRAM (SLDRAM), and Direct Rambus RAM (DR RAM).

[0081] In some embodiments of this application, the computer program 930 may be divided into one or more modules, which are stored in the memory 910 and executed by the processor 920 to perform the method provided in this application. The one or more modules may be a series of computer program instruction segments capable of performing specific functions, which describe the execution process of the computer program 930 in the electronic device.

[0082] like Figure 9 As shown, the electronic device 900 may further include: Transceiver 940, which can be connected to processor 920 or memory 910.

[0083] The processor 920 can control the transceiver 940 to communicate with other devices; specifically, it can send information or data to other devices or receive information or data sent by other devices. The transceiver 940 may include a transmitter and a receiver. The transceiver 940 may further include antennas, and the number of antennas may be one or more.

[0084] It should be understood that the various components in the electronic device 900 are connected through a bus system, which includes a data bus, a power bus, a control bus, and a status signal bus.

[0085] According to one aspect of this application, a computer-readable storage medium is provided that stores computer instructions or programs thereon, which, when executed by a computer, enable the computer to perform the methods of the above-described method embodiments. Alternatively, embodiments of this application also provide a computer program product containing instructions that, when executed by a computer, cause the computer to perform the methods of the above-described method embodiments.

[0086] According to another aspect of this application, a computer program product or computer program is provided, comprising computer instructions stored in a computer-readable storage medium. A processor of a computer device reads the computer instructions from the computer-readable storage medium and executes the computer instructions, causing the computer device to perform the method described in the above-described method embodiments.

[0087] In other words, when implemented using software, it can be implemented wholly or partially in the form of a computer program product. This computer program product includes one or more computer instructions. When these computer program instructions are loaded and executed on a computer, all or part of the processes or functions described in the embodiments of this application are generated. The computer can be a general-purpose computer, a special-purpose computer, a computer network, or other programmable device. The computer instructions can be stored in a computer-readable storage medium or transmitted from one computer-readable storage medium to another. For example, the computer instructions can be transmitted from one website, computer, server, or data center to another via wired (e.g., coaxial cable, fiber optic, digital subscriber line (DSL)) or wireless (e.g., infrared, wireless, microwave, etc.) means. The computer-readable storage medium can be any available medium that a computer can access or a data storage device such as a server or data center that integrates one or more available media. The available medium can be a magnetic medium (e.g., floppy disk, hard disk, magnetic tape), an optical medium (e.g., digital video disc (DVD)), or a semiconductor medium (e.g., solid-state disk (SSD)).

[0088] Those skilled in the art will recognize that the modules and algorithm steps of the various examples described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, or a combination of computer software and electronic hardware. Whether these functions are implemented in hardware or software depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of this application.

[0089] In the several embodiments provided in this application, it should be understood that the disclosed systems, apparatuses, and methods can be implemented in other ways. For example, the apparatus embodiments described above are merely illustrative; for instance, the division of modules is only a logical functional division, and in actual implementation, there may be other division methods. For example, multiple modules or components may be combined or integrated into another system, or some features may be ignored or not executed. Furthermore, the coupling or direct coupling or communication connection shown or discussed may be through some interfaces; the indirect coupling or communication connection between apparatuses or modules may be electrical, mechanical, or other forms.

[0090] The modules described as separate components may or may not be physically separate. The components shown as modules may or may not be physical modules; that is, they may be located in one place or distributed across multiple network units. Some or all of the modules can be selected to implement the solution of this embodiment according to actual needs. For example, the functional modules in the various embodiments of this application may be integrated into one processing module, or each module may exist physically separately, or two or more modules may be integrated into one module.

Claims

1. A method for determining intermittent cardiac output, characterized in that, include: Determine the content of signal markers in the input target object; By using an ultrasound detection device placed at least one predetermined site, signal markers in the blood of a target object are detected, and the time-intensity curve of the signal markers is obtained. Based on the content of the signal markers of the input target object, the area under the time-intensity curve of the signal markers, and the concentration of the signal markers, the intermittent cardiac output of the target object is determined.

2. The method according to claim 1, characterized in that, Based on the formula shown in Equation 1), the discontinuous cardiac output of the target object is determined; Equation 1); Where CO represents the intermittent cardiac output of the target object, k1 represents the calibration coefficient, C0 is the concentration of the signal marker, and V inj This indicates the content of signal markers in the input target object. This represents the area under the time-intensity curve of the signal marker during the time interval t1-t2.

3. The method according to claim 1 or 2, characterized in that, The predetermined sites include: the carotid artery, the left ventricular outflow tract, the renal artery, and the distal digital arteries.

4. The method according to claim 1 or 2, characterized in that, The signal markers are selected from ultrasound contrast agents; Optionally, the ultrasonic testing device is selected from an ultrasonic probe.

5. A method for determining the output quantity of a continuous heart, characterized in that, include: Determine the blood flow waveform at at least one predetermined site of the object to be examined, and obtain the blood flow velocity-time curve; Based on the area under the blood flow velocity-time curve, the vascular radius of the subject under test, the heart rate of the subject under test, and the first intermittent cardiac output, the continuous cardiac output of the subject under test is determined. The first intermittent cardiac output is obtained by the method described in any one of claims 1-4.

6. The method according to claim 5, characterized in that, Based on the formula shown in Equation 2), the discontinuous cardiac output of the target object is determined; Equation 2); Where CCO represents the continuous cardiac output of the subject; k2 represents the correction coefficient; HR represents the heart rate of the subject; VTI represents the area under the curve of the blood flow velocity-time curve; and r is the radius of the blood vessel of the subject.

7. The method according to claim 6, characterized in that, The correction coefficient k2 is the ratio of the first intermittent cardiac output to the second intermittent cardiac output within a predetermined time period; The second intermittent cardiac output is determined by the area under the blood flow velocity-time curve within a predetermined time period, the vascular radius of the subject under test, and the heart rate of the subject under test.

8. A device for determining intermittent cardiac output, characterized in that, include: The signal marker content determination module is used to determine the signal marker content of the input target object; The detection module is used to detect signal markers in the blood of a target object using an ultrasound detection device placed at least one predetermined site, and to obtain the time-intensity curve of the signal markers. The intermittent cardiac output calculation module is used to determine the intermittent cardiac output of the target object based on the content of the signal markers of the input target object, the area of ​​the time-intensity curve of the signal markers, and the concentration of the signal markers.

9. A device for determining the output quantity of a continuous pulse, characterized in that, include: The blood flow waveform determination module is used to determine the blood flow waveform at at least one predetermined location of the object under test and obtain the blood flow velocity-time curve. The continuous cardiac output calculation module is used to determine the continuous cardiac output of the subject based on the area of ​​the blood flow velocity-time curve, the vascular radius of the subject, the heart rate of the subject, and the first intermittent cardiac output. The first intermittent cardiac output is obtained by the method described in any one of claims 1-4.

10. An electronic device, characterized in that, include: Processor and memory; The memory is used to store computer programs; The processor is configured to execute the computer program to implement the intermittent cardiac output determination method as described in any one of claims 1 to 4, or the continuous cardiac output determination method as described in any one of claims 5 to 7.

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