System and method for evaluating cardiac system by determining minimum ratio pd / pa (distal pressure / arterial pressure)

Abstract

To provide, in part, a computer-based method and a system suitable for evaluating a cardiac system using a diagnostic metric such as a pressure value-based ratio.SOLUTION: Selection of a subset or portion of a cardiac cycle is avoided in one embodiment to increase reliability and usability of a diagnostic ratio and parameters described in this description. In one embodiment, a minimum or a relative extrema of a series of diagnostic metrics plotted on a per cycle basis are used to inform diagnosis of a stenosis or other intravascular event or phenomena.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] The present application relates to a system and method for assessing the cardiac system by determining the minimum distal pressure / arterial pressure (PD / PA) ratio.

[0002] Related Applications This application claims the benefit of priority under U.S.C. 119(e) to U.S. Provisional Patent Application No. 62 / 042,448, filed August 27, 2014, the disclosure of which is incorporated herein by reference in its entirety. [Background technology]

[0003] Coronary artery disease is one of the leading causes of death worldwide. The ability to more effectively diagnose, monitor, and treat coronary artery disease is critical to saving lives. Various technologies can be used to acquire intravascular data, such as measuring parameters or signals suitable for imaging or characterizing arteries. Measuring or sensing devices, such as pressure or flow sensors (or other intravascular devices), can be used to collect data and measure cardiovascular and vascular parameters, such as length, diameter, and other parameters. Other data acquisition modalities, such as imaging modalities, can also be used to aid in the diagnosis of stenosis and other cardiac phenomena.

[0004] Intravascular optical coherence tomography (OCT) is a catheter-based imaging modality that uses light to peer into the walls of coronary arteries and generate images for examination. OCT utilizes coherent light, interferometry, and micro-optics to provide video-rate, in vivo tomographic imaging of diseased vessels with micrometer-level resolution. This is achieved by pulling the OCT probe back through the artery of interest to capture its details. OCT images provide high-resolution visualization of coronary artery morphology and can be used alone or in combination with other information, such as pressure data or other data collected using sensing devices. Ultrasound-based devices, such as intravascular ultrasound (IVUS) systems and probes, can also be used to gather information about a subject's cardiovascular system, such as by imaging or measuring arteries. OCT, IVUS, and pressure data for a given cardiovascular system provide a significant amount of data about the given cardiovascular system and its subsystems and components.

[0005] To help simplify and distill the information available to clinicians or end users of OCT, IVUS, pressure sensing, and other intravascular data collection tools and devices, it would be useful to identify new diagnostic metrics that advance the fields of cardiovascular intervention and other research while avoiding unnecessary complexities and assumptions.

[0006] The present disclosure addresses these and other challenges. Summary of the Invention

[0007] In part, the present disclosure relates to computer-based methods and systems suitable for evaluating the cardiac system using pressure-based ratios or other diagnostic metrics as described herein. Pressure-based ratios can be determined using a proximal pressure, identified as Pa, which may include aortic pressure, and a distal pressure, Pd, such as a pressure value obtained at a region downstream of a stenosis. These pressure values ​​can be obtained by sampling two pressure data sources. Some exemplary pressure data sources can include pressure sensors, such as electrical or optical pressure transducers. Suitable pressure sensors can be located on, within, or otherwise relative to a catheter, such as a delivery catheter, an intravascular data collection probe, a guidewire, and other suitable devices and systems. A Pd / Pa ratio can be determined for each sampled Pd and Pa value for one or more cardiac cycles. A minimum value for each such Pd / Pa ratio can be determined for each cardiac cycle. A set of such minimum values, also referred to as MCR values, can be plotted over time. MCR values ​​can be displayed numerically or used as input values ​​to generate other ratios or indices related to cardiac cycle behavior.

[0008] In part, the present disclosure relates to a method for tracking cardiac cycle events using intravascular data, the method including sampling an intravascular data collection probe at a sampling rate to obtain a first plurality of pressure values ​​from a distal region of a blood vessel, receiving in an intravascular data processing system a second plurality of pressure values ​​obtained from a proximal region of the blood vessel, determining a plurality of distal pressure to proximal pressure (Pd / Pa) ratios from the first and second plurality of pressure values, determining a minimum Pd / Pa ratio from the plurality of Pd / Pa ratios, and displaying the minimum Pd / Pa ratio (MCR).

[0009] In one embodiment, the displayed MCR is a ratio for a first cardiac cycle, and the method further includes determining a plurality of MCRs per cardiac cycle. In one embodiment, the method further includes displaying an angiographic cine and the plurality of MCRs over time as the pressure wire is pulled back through the blood vessel. In one embodiment, the method further includes repeating the above steps for a plurality of subsequent cardiac cycles to determine a plurality of MCRs and plotting the plurality of MCRs over time for each cardiac cycle. In one embodiment, the sampling rate is in the range of about 25 Hz to about 2 kHz. In one embodiment, the method further includes filtering the generated waveform using a plurality of Pd / Pa ratio values ​​before determining one or more minimum Pd / Pa ratios per cardiac cycle. In one embodiment, the present disclosure relates to diagnostic metrics that correlate with a patient's state of interest determined using measurements taken during a resting state without a hyperemic agent. In one embodiment, the present disclosure relates to diagnostic metrics that correlate with a patient's state of interest determined using measurements taken during a resting state with a hyperemic agent.

[0010] In one embodiment, the MCR is a stenosis diagnostic metric, and the method further includes monitoring the MCR value over a period of time (T) and identifying changes in the MCR value as an indication of a stenosis in the blood vessel. In one embodiment, the method further includes filtering a waveform generated using the plurality of Pd / Pa ratio values ​​with a filter having a time constant (TC) and setting the time constant to correspond to a portion of the duration of a cardiac cycle. In one embodiment, the TC can be in a range from about 1% to about 50% of the length of a cardiac cycle. In one embodiment, the first plurality of pressure values ​​and the second plurality of pressure values ​​are obtained during one or more cardiac cycles including diastole and systole. In one embodiment, the method includes displaying a user interface including a first panel and a second panel, the first panel including a cycle-by-cycle plot of the MCR value, and the second panel including one or more of the FFR value, the Pd value, the Pa value, the time value, and the MCR value.

[0011] In part, the present disclosure relates to a method for analyzing cardiac cycle events in response to ratios based on pressure values, the method including receiving a first pressure value (Pd1) measured at a location distal to a vascular region, receiving a second pressure value (Pa1) measured at a location proximal to the vascular region, determining a first ratio (R1) between the first and second pressure values, where R1 corresponds to a first time value, receiving a third pressure value (Pd2) measured at a location distal to the vascular region, receiving a fourth pressure value (Pa2) measured at a location proximal to the vascular region, and determining a second ratio (R2) between the third and fourth pressure values, where R2 corresponds to a second time value, and displaying R1 or a plot of R1 versus time if R1 is greater than R2, or displaying R2 or a plot of R2 versus time if R2 is greater than R1. In one embodiment, if R1 is greater than R2, the first time value corresponds to the occurrence of a pressure drop in a cardiac cycle. In one embodiment, the pressure drop is a local maximum. In one embodiment, the pressure drop is a maximum over multiple cardiac cycles. In one embodiment, the method includes displaying a user interface including a first panel and a second panel, the first panel including a cycle-by-cycle plot of MCR values, and the second panel including one or more of an FFR value, a Pd value, a Pa value, a time value, and an MCR value, wherein the MCR value is R1 or R2.

[0012] In part, this disclosure relates to an intravascular data collection system that includes an intravascular data collection system including an interface for receiving data from an intravascular probe, a display system in electrical communication with the intravascular data collection system, one or more memory storage devices containing instructions for outputting a user interface on the display system, the user interface including one or more areas for displaying a minimum cycle ratio or a plot of the minimum cycle ratio, and a processor in electrical communication with the intravascular data collection system, the display system, and the one or more memory storage devices, the processor being programmed to: sample a plurality of proximal pressure values ​​(Pa) per cardiac cycle, sample a plurality of distal pressure values ​​(Pd) per cardiac cycle, determine a set of Pd / Pa ratios for one or more of the sampled Pa and sampled Pd, and identify a minimum ratio value in the set. Some non-limiting examples of intravascular data acquisition and analysis systems or components thereof include the RadiAnalyzer, RadiAnalyzerXpress, Quantien, pressure wire systems (such as Aeris1, Aeris2, or Certus), multimodal systems such as the Optis system, combined intravascular imaging and pressure monitoring systems, and hemodynamic displays with pressure data inputs. Embodiments of the present disclosure may employ dedicated processors and computer devices used in pressure sensing, OCT, or IVUS systems to measure applicable data, determine one or more diagnostic metrics, and generate outputs and intermediate steps to display those diagnostic metrics as discrete fixed or time-varying values. In one embodiment, the intravascular data analysis or data acquisition system is selected from the group consisting of an intravascular pressure sensing system, an optical coherence tomography system, and an intravascular ultrasound system. In one embodiment, the processor is selected from the group consisting of a pressure sensing system processor, an OCT system processor, a multimodal intravascular system processor, and an IVUS system processor. [Brief explanation of the drawings]

[0013] [Figure 1] FIG. 1 is a schematic diagram of an intravascular data collection and display system including a plot based on a minimum or threshold value of a ratio of pressure values, according to an exemplary embodiment of the present disclosure. [Figure 2A] 1 is a flowchart of an exemplary method of intravascular data analysis and display according to an exemplary embodiment of the present disclosure. [Figure 2B] 1 is a flowchart of an exemplary method of intravascular data analysis and display according to an exemplary embodiment of the present disclosure. [Figure 3A] 1 is a series of intravascular data sets or plots according to an exemplary embodiment of the present disclosure. [Figure 3B] 1 is a series of intravascular data sets or plots according to an exemplary embodiment of the present disclosure. [Figure 3C] 1 is a series of intravascular data sets or plots according to an exemplary embodiment of the present disclosure. [Figure 3D] 1 is a series of intravascular data sets or plots according to an exemplary embodiment of the present disclosure. [Figure 3E] 1 is a series of intravascular data sets or plots according to an exemplary embodiment of the present disclosure. [Figure 3F] 1 is a series of intravascular data sets or plots according to an exemplary embodiment of the present disclosure. [Figure 4A] 1 is a display of information and relationship data based on intravascular data over time and per cardiac cycle as described herein in accordance with an exemplary embodiment of the present disclosure. [Figure 4B] 1 is a display of information and relationship data based on intravascular data over time and per cardiac cycle as described herein in accordance with an exemplary embodiment of the present disclosure. [Figure 5A] 1 is an exemplary plot showing blood flow patterns in the left coronary artery system, including a diagnostic information display panel or interface according to an exemplary embodiment of the present disclosure. [Figure 5B]1 is an exemplary plot showing blood flow patterns in the right coronary artery system, including a diagnostic information display panel or interface according to an exemplary embodiment of the present disclosure. DETAILED DESCRIPTION OF THE INVENTION

[0014] The drawings are not necessarily to scale, emphasis instead being placed upon illustrating exemplary principles. The figures are to be considered in all respects as illustrative and are not intended to limit the disclosure. The scope of the present invention is defined solely by the claims.

[0015] Various data acquisition and analysis systems are available for obtaining information about the coronary artery system. Data acquired from a blood vessel using a device or derived from intravascular or extravascular measurements related to that vessel can be analyzed and displayed to provide correlation and extrapolation to assist researchers and clinicians. For example, various measurement systems and intravascular probes are available for determining the fractional flow reserve (FFR) for a blood vessel using pressure sensor-based devices. Intravascular ultrasound (IVUS) can also be used with probes to image portions of a blood vessel. Optical coherence tomography (OCT) is an imaging modality that uses interferometry to obtain distance measurements to a blood vessel or an object placed within that vessel.

[0016] Intravascular data collection devices can be used to generate and receive signals containing diagnostic information for the vessel they are used in. These devices can include, but are not limited to, imaging devices such as optical or ultrasound probes, pressure sensor devices, and other devices suitable for collecting data about blood vessels or other components of the cardiovascular system.

[0017] In part, the present disclosure relates to an intravascular data collection system and associated methods in which intravascular data collected by an intravascular probe can be transformed or analyzed by a processor-based system. The results of such analysis and transformation can be displayed to an end user in various representations, such as on a display in communication with or as part of a system, such as a pressure monitoring system or intravascular data collection system. An example of such a system is shown in Figure 1. In part, the disclosure relates to using such data to generate one or more indices or ratios that correlate with a patient's physiological condition.

[0018] These ratios or indices are correlated with one or more cardiac system parameters or patient conditions, such as stenosis, treatment regimen, stent, stent maladaptation, stenosis severity, stenosis location, infarct size, infarct severity, guided treatment strategy, treatment efficacy assessment, and diagnostic information, to assess the need for additional therapy after treatment. The ratios described herein, in one embodiment, can be determined using pressure values ​​obtained while the subject is in a resting state. In another embodiment, the ratios described herein can be determined after the introduction of a hyperemic agent, such as adenosine. The use of a hyperemic agent, in one embodiment, can amplify the associated waveform.

[0019] In one embodiment, the Pd / Pa ratio is continuously calculated using samples of Pd pressure values ​​or other sampled data obtained from one or more pressure sensors used to calculate the pressure values. In one embodiment, pressure data is collected using an intravascular data collection probe placed in the subject's artery. Exemplary intravascular data collection probes include catheter-based or catheter-delivered probes, guidewire-based probes, imaging probes, ablation probes, ultrasound probes, interferometry-based probes, and other suitable data collection probes and devices. Pa values ​​are continuously obtained from a guide catheter or delivery catheter. The guide catheter or delivery catheter is used to position and advance the intravascular probe through a region of interest in the artery, such as a stenosis. This ratio can be calculated sample by sample, allowing one or more Pd / Pa ratios to be determined during each cardiac cycle. This results in multiple Pd / Pa ratios or sets of Pd / Pa ratios for a given cardiac cycle.

[0020] In the set of Pd / Pa ratios, a minimum Pd / Pa ratio value can be identified. This minimum ratio corresponds to a particular cardiac cycle and can be identified as a minimum cycle pressure ratio index or minimum cycle ratio (MCR). Each MCR for the set of cardiac cycles can be displayed numerically or plotted on a display system as described herein. In one embodiment, each MCR is based on a cardiac cycle rather than a subset or portion of a cardiac cycle. In one embodiment, the MCR is a diagnostic metric generated using sampled intravascular data, such as pressure data. In one embodiment, the sampled data is obtained during diastole and systole.

[0021] As an example, if a sampling rate of 100 Hz is used to collect Pd and Pa data, for an exemplary 1-second cardiac cycle, the cycle will include approximately 100 sample points. These 100 points can be used to determine 100 Pd / Pa ratios. From the set of 100 ratios, the minimum ratio for that cardiac cycle can be identified as the MCR. This process is repeated for multiple cardiac cycles and plotted over time, for example, as shown in FIG. 4A. In one embodiment, the sampling rate ranges from about 10 Hz to about 100 Hz. In one embodiment, the sampling rate ranges from greater than about 25 Hz. In one embodiment, the sampling rate ranges from about 100 Hz to about 2000 Hz. Additionally, cardiac cycles can be analyzed using flow curves, EKGs, pressure waveforms, and other metrics in connection with using the MCR value to diagnose one or more conditions of interest in a subject.

[0022] In one embodiment, the method for determining the ratio as disclosed herein may not involve or rely on ECG triggering or landmark identification. In one embodiment, the method for determining the ratio as disclosed herein may detect heart rate as an input for adjusting filter parameters, such as sampling period, time constant, or other filter parameters. In one embodiment, ECG triggering or landmark identification is used to determine heart rate or other input parameters for the system and method. In another embodiment, the maximum pressure drop in a cardiac cycle can also be identified using the methods and systems disclosed herein, regardless of where such maximum pressure drop occurs in a given cardiac cycle. Thus, rather than being determined solely with respect to diastole, the minimum cycle ratio and related methods of the present disclosure can identify when and where the maximum pressure drop occurs in a given cardiac cycle. This identification can be performed regardless of whether such pressure drop occurs in diastole or systole.

[0023] Thus, embodiments of the present disclosure provide greater flexibility and improved accuracy over other approaches, as the method and associated ratios are independent of whether the pressure values ​​used to determine the ratio are measured in the left or right coronary artery system. Some exemplary graphs of flow details associated with the right and left coronary artery systems are shown in Figure 5. Compared to metrics that use pressure averaging over several cardiac cycles, the minimum cycle ratio can also be more sensitive to changes that occur when the sensor is pulled back across a lesion. Thus, after a revascularization procedure occurs, or during pressure pullback, the minimum cycle ratio can be more sensitive to pressure changes when compared to full-cycle Pd / Pa. This sensitivity, in which smaller pressure drops are displayed as larger amplitude values ​​on the display system, is useful when tracking MCR values ​​during pullback to identify the location of a stenosis, assessing the effects of stent placement, evaluating side branches, and dilating disease or other vascular features. Greater sensitivity also allows for easier detection of pressure changes, for example, when a stenosis is identified based on changes in MCR.

[0024] In one embodiment, to improve the consistency of the MCR value for a given minimum cycle ratio, this ratio may optionally be averaged over multiple cardiac cycles. In one preferred embodiment, the MCR is determined cycle-by-cycle rather than averaged over multiple cardiac cycles. The MCR may be displayed as an on-screen number, a curve, a plot of discrete points, and a combination of the foregoing or other representations correlated to or derived from the MCR based on the MCR.

[0025] In one embodiment, the display system provides a user interface that includes functionality that allows specific conditions or other parameters to be used when determining the MCR or other ratio. After recording the value or trigger, the system can be configured to display the lowest ratio for the entire recording, i.e., after a preselected number of heart rates based on user selection via the user interface. Each MCR value provides a metric for identifying the occurrence of the maximum pressure drop in a cardiac cycle, cycle by cycle, regardless of pressure sensing location and without ECG triggering or landmark identification. An exemplary system and its components for determining MCR values ​​are described with respect to FIG. 1.

[0026] 1 illustrates a catheterization system 10 suitable for analyzing the cardiac system. System 10 can include various systems, such as a data acquisition and analysis system 18, an interface system 20, a display system 22, and an x-ray system 25, such as an angiography system 25. The intravascular data acquisition and analysis system 18 or components thereof can include multimodal systems, such as the RadiAnalyzer, RadiAnalyzerXpress, Quantien, the Aeris system, the Optis system, combined intravascular imaging and pressure monitoring systems, and hemodynamic displays with pressure data input.

[0027] The data acquisition and analysis system 18 may include hardware components such as a processor 23, such as a microprocessor; memory 26; a filter 32 having an associated time constant TC; and one or more software modules (e.g., a Pd / Pa ratio hardware element or software module 29), circuits, or diagnostic metric generators 29. The processor may be in electrical communication with a circuit board of a pressure-sensing, OCT, IVUS, or other intravascular data acquisition system. The time constant TC may be updated or adapted based on measured parameters or preset values, or may be user-selected. The data acquisition and analysis system 18 may also review historical data stored in a database 35 from previous intravascular and extravascular data acquisition sessions. Results of determining one or more ratios, curves, or other values ​​as described herein may also be stored in the database 35. One or more databases may be used for various applicable data sets.

[0028] In part, embodiments of the present disclosure relate to various features of pressure sensing devices, measurement systems, and associated software suitable for determining the ratio based on signals sampled from an intravascular data collection probe, such as probe 40 or 44. Pressure monitoring can be performed using guidewire-based probes 40, 44 having semiconductor devices including components that undergo electrical changes in response to pressure changes. The embodiments described herein support methods for performing the method, ratio determination, and measurement using the guidewire-based probes and associated software and electrical elements of data collection and analysis system 18. Data received by interface system 20, system 18, or system 22 can be transmitted using wired probe 44 or wireless probe 40. A sensor 45, such as a proximal pressure sensor on a guide or delivery catheter, can also receive a proximal pressure value (Pa), such as an aortic pressure value.

[0029] System 18 can perform measurement calculations based on sampled signals from the intravascular probe. Alternatively, system 18 can receive signals encoding the results of calculations performed using circuitry or processing elements located on the probe, such as the probe's proximal connector. System 18 can also include software, a control system, data analysis and display equipment, and a processor suitable for graphically displaying pressure values, FFR values, MCR values, sampled Pa values, sampled Pd values, running averages related to the above, and other values.

[0030] The interface system 20 is connected to one or more circuits or signal processing or control elements. These circuits, elements, and other components of a given intravascular measurement system are used to convert time-varying electrical signals from the probes 40, 44 or guidewire-based probes by sampling sensors to generate Pd and Pa values ​​that can be received by one or more of the systems of FIG. 1. The time-varying electrical signals can be current changes, voltage changes, resistance changes, or other data that correlate to MCR values. The interface and display are formatted and programmed to display these values, as well as other ratios and parameters, as described herein, using the display system 22.

[0031] Display system 22 may include panels, user interfaces, and other screens suitable for displaying pressure data such as Pd and Pa values ​​or data derived therefrom 55, 58, intravascular images 70, IVUS or OCT images 67, 65, and other intravascular images and data. Display 22 or interface 20 may be part of or in electrical communication, such as wireless communication, with system 18 to receive data from guidewire-based probes, OCT, FFR, IVUS, or other systems.

[0032] The angiography system 25 can be used to generate cine sequences that can be viewed before and after data collection pullback via the pressure wire. In one embodiment, the display system simultaneously displays the cine sequence while displaying the time-varying MCR values ​​as the pressure sensor is pulled back through the vessel. The changes in the MCR values ​​can be used to determine stenotic regions along the arterial pullback path. These stenotic locations can be identified using a cursor or electronic annotation tool to mark candidate regions for stent placement on one or more angiographic frames of the cine sequence or for further imaging using IVUS, OCT, or another imaging or data collection modality.

[0033] Pa pressure values ​​obtained from pressure sensors mounted on a catheter or guidewire, or calculated using other measurements, can be used along with Pd pressure values ​​sampled from a given intravascular probe to determine one or more ratios, such as MCR values. These ratios can be displayed or plotted as described herein. Figures 2A and 2B show exemplary methods 100 and 150, respectively, for determining such one or more ratios. While the ratios are described here as minimum values, the values ​​can also be determined as falling within a particular threshold or other range, such as within a certain percentage of an absolute minimum or within a standard deviation from a minimum value.

[0034] While a minimum value is preferred in certain circumstances, in situations where a minimum value is referenced herein, a threshold value that is not the minimum value but is a predetermined threshold within the minimum value range may be used. Thus, in one embodiment, a threshold value between about 0% and about 20% of a minimum value, such as a Pd / Pa ratio, may be used for each cycle. In one embodiment, the Pd / Pa ratio is a diagnostic metric that can be displayed on a user interface or display panel of an OCT, IVUS, pressure sensing, flow sensing, or other system. The diagnostic metric facilitates subject decision-making for a user, such as a clinician.

[0035] As shown in FIG. 2A, the method includes receiving a Pa value and a Pd value. Steps A1 and A2 can be performed separately or together. The values ​​can be received by a component of system 10, such as data acquisition and analysis system 18. In one embodiment, multiple Pd and Pa values ​​are received over time and associated with individual cardiac cycles during collection. The method also includes determining a Pd / Pa ratio (Step B) based on the received Pa and Pd values. In one embodiment, multiple Pd / Pa ratios are determined. An optional filtering step (Step C) can be part of the method. Filtering the Pd / Pa ratio trajectory or curve can smooth such trajectory or curve by removing noise. The filter can be of various types, such as a low-pass filter, a high-pass filter, a moving average filter, similar filters, or combinations thereof, and other suitable filters. The time constant Tc of the filter can range from about 10 ms to about 500 ms.

[0036] In one embodiment, applying a filter to this ratio curve improves the reproducibility of the MCR value for a given cardiac cycle. In one embodiment, the time constant TC influences the MCR value. This is important, for example, when a patient's heart rate, bradycardia, or tachycardia fluctuates widely. In one embodiment, the time constant TC can be a preselected constant having a TC range of about 10 ms to about 500 ms, preferably a subset of 100 to 300 ms. In one embodiment, the TC can be adaptive, changing over time, or have a relationship to one or more parameters, such as cardiac cycle length, or other cardiac or vascular parameters. For example, an adaptive TC determined as a percentage of cardiac cycle length can be used. Cardiac cycle length is measured during a data collection session and used as an input to generate the adaptive TC. The adaptive TC can take the form TC=a(cardiac cycle length), where a is a percentage. Such an adaptive TC percentage can range from about 1% to about 50% of cardiac cycle length. The TC can be adjusted by the user via a user interface, can be a fixed value stored in the data collection system, can be updateable over the network or via firmware update, or can be configured to suit a given scenario. The user interface can be displayed on the system 10 via the display 22.

[0037] 2A , if one or more Pd / Pa ratios have been determined, the method also includes determining a minimum Pd / Pa ratio (MCR) (step D). In one embodiment, the minimum value, relative extreme value, or a value correlated or derived therefrom may be used as a diagnostic metric. A threshold, such as a percentage of the minimum ratio, may also be used in this and other MCR determination embodiments. This determination process may be performed over time, for each cardiac cycle. Once one or more MCR values ​​have been determined, these ratios may be displayed numerically or plotted over time on a display system, as shown in the figures of this disclosure (step E). FIG. 2B illustrates another exemplary embodiment of a method 160 for determining and displaying an MCR. Steps 50 and 55 may be performed together or separately. Step 65 is an optional filtering step. Steps 60, 70, and 80 may be performed as shown. The process of FIG. 2B further illustrates that the multiple MCRs can be displayed on a display as discrete points, values, or curves over time for N cardiac cycles, as shown in process flow 200. In method 200, steps 210 and 220 are performed. Noise filtering can also be performed as part of method 200. Thus, steps include sampling multiple pressure values ​​measured distally for a cardiac cycle. Sampling multiple pressure values ​​measured proximally for a cardiac cycle is a separate step. Determining multiple ratios using the sampled distal pressure values ​​and the sampled proximal pressure values ​​for each ratio is a step. Optionally, noise filtering can be performed. A minimum ratio can be determined from the multiple ratios for a cardiac cycle. This ratio can then be displayed as a value, a changing value, or a plot of values ​​or points. The repeated sampling, ratio determination, and minimum ratio determination for N cardiac cycles can be performed iteratively for one or more N cycles. In one embodiment, the method includes displaying the N minimum ratios for each cardiac cycle as time ratios.

[0038] FIG. 3A shows a plot of Pa and Pd values ​​sampled over multiple cardiac cycles. The Pa curve generally lies above the Pd curve. FIG. 3B shows the plot of FIG. 3A with the addition of a curve corresponding to the Pd / Pa ratio. In FIG. 3C, the plot of FIG. 3B is shown with the addition of a moving average of the Pd / Pa ratio. In FIG. 3C, the Pd / Pa curve is smoothed by applying a filter with a time constant TC before determining the moving average. Applying such a filter is optional, but may be advantageous in certain scenarios to increase the reproducibility of MCR measurements regardless of signal noise or fluctuating heart rate. In FIG. 3D, the plot of FIG. 3C is shown with the addition of vertical markers corresponding to the minimum Pd / Pa ratios for two cardiac cycles. These minimum values ​​can be plotted as MCR values ​​over time, as shown in FIG. 3F or in FIGS. 4A and 4B. The images shown in FIGS. 3A-3D illustrate how data can be generated using the MCR determination method as disclosed with respect to FIGS. 2A and 2B. These diagrams, or portions thereof, may also be displayed to the user or derivatives thereof to facilitate diagnosis of the subject.

[0039] Figure 3E shows a plot of FFR values. The FFR values ​​range from approximately 0.6 to approximately 1.0. The FFR values ​​are plotted against time, and the FFR value is calculated for each sample. The FFR value was determined using the Pd / Pa ratio during hyperemia and averaged for one or several cardiac cycles over the recorded cardiac cycle. Measurement of the flow reserve ratio (FFR) using a pressure wire is used to guide the decision to implant a coronary stent. A distal FFR reading of 0.8 or greater at a coronary artery bifurcation indicates that the bifurcation lesion has not narrowed sufficiently to induce ischemia under hyperemic conditions, and percutaneous coronary intervention (PCI) can be safely postponed. Conversely, a distal FFR value below 0.8 typically indicates the need for treatment with stent implantation. Transitions in the MCR value can be used in parallel with, or instead of, the FFR value to facilitate stent planning.

[0040] 3F shows a plot of discrete MCR values ​​versus time. In the illustrated embodiment, the MCR values ​​are discrete because they are determined for each cardiac cycle. The MCR value is determined as the minimum Pd / Pa ratio for the sampled Pd and Pa values ​​for a given cardiac cycle.

[0041] Figure 4A and its alternative graphical representation, Figure 4B, also show the FFR values ​​of Figure 3E and the MCR values ​​of Figure 3F in the bottom panel of the screen. Sampled Pd and Pa values ​​are displayed as traces in the top panel. Additionally, a moving average of the Pa values ​​(Pa moving average) and a moving average of the Pd values ​​(Pd moving average) are also shown. The Pa moving average is a curve passing through the Pa peak and the Pd peak. The Pd moving average is a curve positioned below the Pa moving average. In the right-hand area of ​​the screen, from top to bottom, Pa, Pd, FFR, MCR, and time values ​​are shown corresponding to the position of a vertical marker VM. The vertical marker VM can be programmed to display a predetermined value or adjusted to cycle through a set of preset positions. The vertical marker VM can also be positioned by the user. As shown, VM is near the minimum Pd / Pa and minimum MCR values. In one embodiment, multiple panels of data or user interface information such as those shown in Figures 4A and 4B are displayed with plots or fixed or time-varying values ​​of MCR, Pa, Pd, FFR, time, Pa shift, Pd shift, and averages and weighted combinations thereof. In one embodiment, a display panel containing time-varying MCR values ​​is plotted against time-varying FFR values ​​to facilitate stent planning or other characterization or diagnosis of the artery.

[0042] These diagrams and user interface screens can be used in conjunction with intravascular and angiographic images to make stent decisions, identify areas of interest from a diagnostic perspective, and as a diagnostic tool to inform other cardiac treatment decisions. These ratios are also advantageous for the various implementations and reliability details described herein compared to other approaches.

[0043] 4A and 4B show MCR at both rest and hyperemia (MFR values ​​are determined simultaneously with FFR). The MCR determined in a subject at rest can be used to predict FFR values ​​during hyperemia. Furthermore, the MCR during hyperemia, compared to the FFR, can be used to amplify the pressure difference induced by a stenosis during hyperemia. In one embodiment, a user of the systems, methods, and displays disclosed herein can review a given display of MCR values ​​over time before, during, or after a procedure to diagnose the severity of the stenosis, the location of the stenosis, guide treatment strategies, evaluate treatment efficacy, and assess the need for additional treatment after a procedure.

[0044] 5A and 5B are exemplary plots showing blood flow patterns in the left and right coronary artery systems. In FIG. 5A, blood flow in the left coronary artery is shown in terms of blood volume per unit time versus time. In FIG. 5B, blood flow in the right coronary artery is shown in terms of blood volume per unit time versus time. The ratios and indices disclosed herein are suitable for describing one or more cardiac cycles and are suitable for use with pressure data collected from either the left or right coronary artery, even if the flow characteristics of the two vessels differ over time. In one embodiment, the plots of FIGS. 5A and 5B can be displayed as part of the display or user interface of an OCT, IVUS, tonometry, flowmetry, or other cardiovascular diagnostic / data acquisition system described herein.

[0045] In one embodiment, the diagnostic metrics described herein are not specific to a cardiac cycle phase, such as diastole. The "instantaneous wave-free ratio," or iFR, is a method that attempts to correlate iFR with the more widely used fractional flow reserve, or FFR. In contrast to one embodiment of the present disclosure, as part of the process of calculating the instantaneous wave-free period, aortic and coronary pressures are averaged during diastole. This iFR methodology is based on the assumption that vascular resistance is minimized during diastole, thus allowing lesion assessment at rest without the use of hyperemic dilators.

[0046] There are challenges and uncertainties associated with using ratios that do not include instantaneous waves. Calculating a ratio during a specific window of diastole requires precise gating of the signal, such as by searching for specific values ​​in the pressure waveform. Using such ratios increases the complexity of signal processing and waveform analysis, and reliance on diastole can distort the output. Furthermore, as noted above, using ratios calculated during diastole is based on the assumption that maximum blood flow occurs during diastole. While this is not necessarily true in the right coronary system, where flow rates can be higher during systole, using diastolic metrics in the right coronary vasculature can potentially lead to an erroneous assessment of lesion severity. Diastole is a subset of the cardiac cycle. As a result, relying on data collected during a fixed subset of the cardiac cycle can lead to unreliable results under various circumstances. In one embodiment, the diagnostic methods and associated output metrics described herein are not obtained using such a fixed subset of the cardiac cycle. In one embodiment, the disclosed method generates a diagnostic metric based on one or more cardiac cycles or a subset of cardiac cycles that includes diastole and systole.

[0047] Non-limiting software features and embodiments for determining diagnostic metrics such as ratios and indices based on intravascular probe data. The following description is intended to provide a general overview of device hardware and other operating elements suitable for carrying out the methods of the present disclosure described herein. This description is not intended to limit the applicable environments or the scope of the present disclosure. Similarly, hardware and other operating elements may be suitable as part of the above-described devices. The present disclosure can be practiced with other system configurations, including personal computers, multiprocessor systems, microprocessor-based or programmable electronic devices, network PCs, minicomputers, mainframe computers, etc. The present disclosure can also be practiced in distributed computing environments where tasks are performed by remote processing devices linked through a communications network, such as different rooms in a catheterization lab or catheterization procedure room.

[0048] Some portions of the detailed descriptions are presented in terms of algorithms and symbolic representations of operations on data bits within a computer memory. These algorithmic descriptions and representations may be used by those skilled in the related arts of computers and software. In one embodiment, an algorithm is herein generally conceived to be a self-consistent sequence of operations leading to a desired result. The operations performed, whether as method steps or otherwise, described herein require physical manipulations of physical quantities. Usually, though not necessarily, these quantities take the form of electrical or magnetic signals capable of being stored, transferred, combined, transformed, compared, and otherwise manipulated.

[0049] As will become apparent from the following description, unless otherwise stated, throughout the specification, discussions utilizing terms such as "processing," "calculating," "correlating," "detecting," "measuring," "calculating," "comparing," "generating," "sensing," "determining," or "displaying," or operations related to Boolean logic or other sets, refer to operations and processes of a computer system or electronic device that convert data represented as physical (electronic) quantities in registers and memories of the computer system or electronic device to other data similarly represented as physical quantities in electronic memory or registers or other such information storage, transmission, or display devices.

[0050] The present disclosure also relates, in some embodiments, to apparatus for performing the operations herein. This apparatus may be specially constructed for the required purposes, or may comprise a general-purpose computer selectively activated or reconfigured by a computer program stored in the computer. Various circuits and components thereof may be used to perform some of the data collection, conversion, and processing described herein.

[0051] The algorithms and displays presented herein are not inherently related to any particular computer or other apparatus. Various general-purpose systems may be used with programs in accordance with the teachings herein, or it may prove convenient to construct more specialized apparatus to perform the required method steps. The required structure for a variety of these systems will appear from the description below. Further, the disclosure is not described with reference to any particular programming language, and various embodiments can be implemented using a variety of programming languages.

[0052] Embodiments of the present disclosure can be realized in many different forms, including, but not limited to, computer program logic for use with a processor (e.g., a microprocessor, microcontroller, digital signal processor, or general-purpose computer), programmable logic for use with a programmable logic device (e.g., a field programmable gate array (FPGA) or other programmable logic device), discrete components, integrated circuits (e.g., application specific integrated circuits (ASICs)), or any other means including any combination thereof. In exemplary embodiments of the present disclosure, some or all of the processing of data collected using an OCT probe and processor-based system can be implemented as a set of computer program instructions, which are converted into a computer-executable form, stored as a computer-readable medium, and executed by a microprocessor under the control of an operating system. In this manner, the query response and input data are converted into processor understandable instructions suitable for sampling intravascular data, including generating fixed or time-varying diagnostic metrics, fixed or time-varying ratios based on sampled pressure values, sampling based on one or more cardiac cycles or subsets of cardiac cycles including diastole and systole, and other indications of how and what changes to determine such ratios and for a given pressure data collection session, as well as other features and embodiments described above.

[0053] Computer program logic implementing all or a portion of the functionality described hereinabove may be implemented in various forms, including, but not limited to, source code form, computer-executable form, and various intermediate forms (e.g., forms produced by an assembler, compiler, linker, or locator). Source code may include a series of computer program instructions implemented in any of a variety of programming languages ​​(e.g., object code, assembly language, or higher-level languages ​​such as Fortran, C, C++, JAVA, or HTML) for use with various operating systems or operating environments. Source code may define and use various data structures and communication messages. Source code may be in computer-executable form (e.g., via an interpreter), or the source code may be converted into computer-executable form (e.g., via a translator, assembler, or compiler).

[0054] A computer program may be fixed in any form (e.g., source code, computer-executable, or intermediate form) permanently or temporarily on a tangible storage medium, such as semiconductor memory (e.g., RAM, ROM, PROM, EEPROM, or flash programmable RAM), magnetic storage medium (e.g., diskette or fixed disk), optical storage medium (e.g., CD-ROM), PC card (e.g., PCMCIA card), or other storage device. A computer program may also be fixed in the form of a signal transmittable to a computer using any of a variety of communications technologies, including, but not limited to, analog, digital, optical, wireless (e.g., Bluetooth), networking, and internetworking technologies. A computer program may be distributed in the form of a removable storage medium accompanied by printed or electronic documentation (e.g., shrink-wrapped software), preloaded with a computer system (e.g., on a system ROM or fixed disk), or distributed from a server or electronic bulletin board via a communications system (e.g., the Internet or World Wide Web).

[0055] Hardware logic (including programmable logic for use with a programmable logic device) implementing all or a portion of the functionality previously described herein may be designed using conventional manual methods, or may be designed, captured, simulated, or documented electronically using a variety of tools, such as computer-aided design (CAD), hardware description languages ​​(e.g., VHDL or AHDL), or PLD programming languages ​​(e.g., PALASM, ABEL, or CUPL).

[0056] Programmable logic may be permanently or temporarily fixed on tangible storage media such as semiconductor memory (e.g., RAM, ROM, PROM, EEPROM, or flash programmable RAM), magnetic memory (e.g., diskette or fixed disk), optical memory (e.g., CD-ROM), or other storage devices. Programmable logic may also be fixed as signals transmittable to a computer using any of a variety of communications technologies, including, but not limited to, analog, digital, optical, wireless (e.g., Bluetooth), networking, and internetworking technologies. Programmable logic may be distributed as removable storage media with printed or electronic documentation (e.g., shrink-wrapped software), preloaded with a computer system (e.g., on a system ROM or fixed disk), or distributed from a server or electronic bulletin board via a communications system (e.g., the Internet or World Wide Web).

[0057] Various examples of suitable processing modules are described in more detail below. As used herein, a module refers to software, hardware, or firmware suitable for performing a particular data processing or data transmission task. Typically, in preferred embodiments, a module refers to a software routine, program, or other memory-resident application suitable for receiving, translating, routing, and processing instructions, or various types of data, such as resistance changes, voltage changes, current changes, guidewire-based probe data, intravascular pressure data, ratios, indices, and other information of interest.

[0058] The computers and computer systems described herein may include operatively associated computer-readable media, such as memory for storing software applications used in acquiring, processing, storing, and / or communicating data. It will be understood that such memory may be internal, external, remote, or local with respect to the operatively associated computer or computer system.

[0059] Memory may include means for storing software or other instructions, including, but not limited to, for example, a hard disk, an optical disk, a floppy disk, a DVD (digital versatile disk), a CD (compact disk), a memory stick, flash memory, a ROM (read only memory), a RAM (random access memory), a DRAM (dynamic random access memory), a PROM (programmable ROM), an EEPROM (extendable erasable programmable read only memory), and / or other similar readable medium.

[0060] In general, computer-readable storage media applied in connection with the embodiments of the present disclosure described herein may include any storage medium capable of storing instructions for execution by a programmable device. Where applicable, method steps described herein may be implemented or performed as instructions stored on a computer-readable storage medium or memory medium. These instructions may be software embodied in various programming languages, such as C++, C, Java, and / or various other types of software programming languages, that may be adapted to create instructions according to embodiments of the present disclosure.

[0061] A storage medium may be non-transitory or may include a non-transitory device. Thus, a non-transitory storage medium or a non-transitory device may include a tangible device, meaning that the device has a concrete physical form, although the device can change its physical state. Thus, for example, non-transitory refers to a device that remains tangible despite this change in state.

[0062] The aspects, embodiments, features, and examples of the present disclosure are to be considered in all respects illustrative and are not intended to limit the disclosure, the scope of which is defined solely by the claims. Other embodiments, modifications, and applications will be apparent to those skilled in the art without departing from the spirit and scope of the disclosure as claimed.

[0063] The use of headings and paragraphs in this application is not meant to limit the disclosure, and each paragraph may apply to any aspect, embodiment, or feature of the disclosure.

[0064] Throughout the application, when a composition is described as having, including, or comprising particular components, or when a process is described as having, including, or comprising particular process steps, it is understood that a composition of the present teachings consists essentially of or consists of the recited components, or a process of the present teachings consists essentially of or consists of the recited process steps.

[0065] In the application, when an element or component is referred to as being included in and / or selected from a list of enumerated elements or components, it is understood that the element or component can be any one of the enumerated elements or components and can be selected from a group consisting of two or more of the enumerated elements or components. Furthermore, it is understood that the elements and / or features of the compositions, devices, or methods described herein can be combined in various ways, either explicitly or implicitly, without departing from the spirit and scope of the present teachings.

[0066] "include, includes, including" or "have, Use of the terms "has, having" should generally be understood to be open-ended and non-limiting unless otherwise specified.

[0067] The use of the singular herein includes the plural (and vice versa) unless specifically stated otherwise. Also, the singular forms "a," "an," and "the" include the plural unless the context clearly dictates otherwise. In addition, when the term "about" is used before a quantitative value, the present teachings also include the specific quantitative value itself unless specifically stated otherwise.

[0068] It should be understood that the order of steps or order for performing certain actions is irrelevant so long as the present teachings remain operable. Moreover, two or more steps or actions may be conducted simultaneously.

[0069] When a range or list of values ​​is provided, each intervening value between the upper and lower limits of that range or list of values ​​is individually contemplated and encompassed within the disclosure as if each value were specifically recited herein. Additionally, smaller ranges between and including the upper and lower limits of a given range are contemplated and encompassed within the disclosure. The listing of exemplary values ​​or ranges is not exclusive of other values ​​or ranges between and including the upper and lower limits of a given range.

[0070] It should be understood that the drawings and descriptions of the present disclosure have been simplified to show elements that are relevant for a clear understanding of the present disclosure, with other elements excluded for clarity. However, one skilled in the art will recognize that these and other elements are desirable. However, because such elements are known in the art and because they do not facilitate a better understanding of the present disclosure, a discussion of such elements is not provided herein. It should be understood that the drawings are presented for illustrative purposes and not as structural diagrams. Omitted details and variations or alternative embodiments are within the knowledge of one skilled in the art.

[0071] In certain aspects of the present disclosure, multiple components may be substituted for a single component, and multiple components may be substituted for a single component to provide an element or structure or to perform a given function(s). Except to the extent that such substitution would not be effective for practicing a particular embodiment of the present disclosure, such substitution is deemed to be within the scope of the present disclosure.

[0072] The examples presented herein are intended to illustrate potential and specific implementations of the present disclosure. It will be understood that these examples are primarily for the purpose of explaining the present disclosure to those skilled in the art. Changes may be made to these diagrams or the operations described herein without departing from the spirit of the present disclosure. For example, in some cases, method steps or operations may be executed or performed in a different order, or operations may be added, deleted, or modified.

[0073] The following describes the contents of the claims as originally filed as an example. [Example 1] 1. A method for tracking cardiac cycle events using intravascular data, the method comprising: sampling the intravascular data collection probe at a sampling rate to obtain a first plurality of pressure values ​​from a distal region of the blood vessel; receiving, at an intravascular data processing system, a second plurality of pressure values ​​obtained from a proximal region of the blood vessel; determining a plurality of distal pressure to proximal pressure (Pd / Pa) ratios from the first plurality of pressure values ​​and the second plurality of pressure values; determining a minimum Pd / Pa ratio from the plurality of Pd / Pa ratios; and displaying the minimum Pd / Pa ratio (MCR). method. [Example 2] 2. The method of example 1, wherein the displayed MCR is a ratio for a first cardiac cycle, further comprising determining a plurality of MCRs for each cardiac cycle. [Example 3] 3. The method of example 2, further comprising displaying an angiographic cine and the plurality of MCRs over time as the pressure wire is pulled back through the blood vessel. [Example 4] 2. The method of example 1, further comprising repeating the steps for a plurality of subsequent cardiac cycles to determine a plurality of MCRs, and plotting the plurality of MCRs over time for each cardiac cycle. [Example 5] 2. The method of claim 1, wherein the sampling rate is in the range of about 25 Hz to about 2 kHz. [Example 6] 2. The method of example 1, further comprising filtering the generated waveform using a plurality of Pd / Pa ratio values ​​before determining one or more minimum Pd / Pa ratios per cardiac cycle. [Example 7] 2. The method of claim 1, wherein the MCR is a stenosis diagnostic metric, further comprising monitoring MCR values ​​over a period of time (T) and identifying changes in the MCR values ​​as an indication of stenosis in the blood vessel. [Example 8] 2. The method of example 1, further comprising filtering a waveform generated using a plurality of Pd / Pa ratio values ​​using a filter having a time constant (TC), and setting the time constant to correspond to a fraction of a cardiac cycle duration. [Example 9] The method according to Example 8, wherein the TC is in the range of about 1% to about 50% of the length of the cardiac cycle. [Example 10] 2. The method of example 1, wherein the first and second plurality of pressure values ​​are obtained during one or more cardiac cycles including diastole and systole. [Example 11] The method of example 1, further comprising displaying a user interface comprising a first panel and a second panel, wherein the first panel comprises a cycle-by-cycle plot of MCR values, and the second panel comprises one or more of FFR values, Pd values, Pa values, time values, and MCR values. [Example 12] 1. A method for tracking cardiac cycle events and one or more diagnostic metrics, the method comprising: receiving a first pressure value (Pd1) measured at a location distal to the vascular region; receiving a second pressure value (Pa1) measured at a location proximal to the vascular region; determining a first ratio (R1) between a first pressure value and a second pressure value, the R1 corresponding to a first time value; receiving a third pressure value (Pd2) measured at a location distal to the vascular region; receiving a fourth pressure value (Pa2) measured at a location proximal to the vascular region; determining a second ratio (R2) between the third pressure value and the fourth pressure value, the R2 corresponding to a second time value; displaying R1 or a plot of R1 versus time if R1 is greater than R2, or displaying R2 or a plot of R2 versus time if R2 is greater than R1; method. [Example 13] 13. The method of example 12, wherein the first time value corresponds to the occurrence of a pressure drop in the cardiac cycle when R1 is greater than R2. [Example 14] 14. The method of claim 13, wherein the pressure drop is a local maximum. [Example 15] The method of example 13, wherein the pressure drop is maximal over multiple cardiac cycles. [Example 16] 14. The method of example 13, comprising displaying a user interface comprising a first panel and a second panel, wherein the first panel comprises a cycle-by-cycle plot of MCR values, and the second panel comprises one or more of FFR values, Pd values, Pa values, time values, and MCR values, wherein the MCR value is R1 or R2. [Example 17] An intravascular data analysis system, the intravascular data analysis system comprising: an intravascular data acquisition system including an interface for receiving data from the intravascular probe; a display system in electrical communication with the intravascular data acquisition system; one or more memory storage devices containing instructions for outputting a user interface on the display system, the user interface including one or more regions for displaying a minimum cycle ratio or a plot of the minimum cycle ratio; a processor in electrical communication with the intravascular data collection system, the display system, and one or more memory storage devices; The processor Multiple proximal pressure values ​​(Pa) are sampled per cardiac cycle. Multiple distal pressure values ​​(Pd) are sampled per cardiac cycle. determining a set of Pd / Pa ratios for one or more of the sampled Pa and sampled Pd; and identifying a minimum ratio value within the set. Intravascular data analysis system. [Example 18] The intravascular data analysis system of Example 17 further comprises a filter having a time constant (TC) and a waveform input, the filter being a noise filter, the time constant being a fraction of the duration of a cardiac cycle, and the filter being in electrical communication with the processor. [Example 19] 19. The intravascular data analysis system of claim 18, wherein the intravascular data collection system is selected from the group consisting of an intravascular pressure sensing system, an optical coherence tomography system, and an intravascular ultrasound system. [Example 20] 18. The intravascular data analysis system of Example 17, wherein the processor is selected from the group consisting of a pressure sensing system processor, an OCT system processor, a multimodal intravascular system processor, and an IVUS system processor.

Claims

1. A catheter examination system (10), comprising: an interface system (20) configured to convert time-varying electrical signals from the guidewire-based pressure sensors (40, 44) to generate distal pressure (Pd) and proximal pressure (Pa) values; a display system (22); a data acquisition and analysis system (18) including a processor (23), a memory (26), a filter (32) having an associated time constant (C), and one or more software modules, circuits, or hardware components, the data acquisition and analysis system (18) being configured to cause the display system (22) to display values ​​of minimum cycle ratios that change over time as the guidewire-based pressure sensor (40, 44) is pulled back through a blood vessel, each minimum cycle ratio being the smallest Pd / Pa ratio within a set of Pd / Pa ratios determined throughout a corresponding cardiac cycle; an angiography system (25) configured to generate a cine sequence; the data acquisition and analysis system is configured to cause the display system (22) to simultaneously display the cine sequence while displaying the value of the minimum cycle ratio as it changes over time as the guidewire-based pressure sensor (40, 44) is pulled back through the blood vessel. A catheterization system (10).

2. 2. The catheterization system of claim 1, wherein the data acquisition and analysis system is configured to display a graph of the value of the minimum cycle ratio as it changes over time during pullback of the guidewire-based pressure sensor.

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