阅读说明：本技术 心房纤颤 (Atrial fibrillation ) 是由 Y·A·阿摩司 M·阿米特 S·戈德堡 L·博策尔 J·亚尼茨基 E·纳卡尔 E·拉文纳 于 2021-06-15 设计创作，主要内容包括：本发明题为“心房纤颤”。本发明提供了一种方法。所述方法由检测引擎实现,所述检测引擎体现在存储在存储器上并由至少一个处理器执行的处理器可执行代码中。所述方法包括对向量速度场建模,所述向量速度场测量并量化经过局部激活时间的心电图数据信号的速度。所述方法还包括：确定平面中每个点的代码以提供色码向量场图像；通过使用内核以扫描所述颜色编码向量场图像来检测病灶指示和转子指示；以及将所述病灶指示和所述转子指示分类成维持灶。(The invention is entitled "atrial fibrillation". The invention provides a method. The method is implemented by a detection engine embodied in processor-executable code stored on a memory and executed by at least one processor. The method includes modeling a vector velocity field that measures and quantifies the velocity of the electrocardiographic data signal over a local activation time. The method further comprises the following steps: determining a code for each point in the plane to provide a color-coded vector field image; detecting a lesion index and a rotor index by using a kernel to scan the color-coded vector field image; and classifying the lesion indication and the rotor indication as a maintenance lesion.)

1. A method implemented by a detection engine embodied in processor-executable code stored on a memory and executed by at least one processor, the method comprising:

modeling, by the detection engine, a vector velocity field that measures and quantifies a velocity of the electrocardiographic data signals over a local activation time;

determining, by the detection engine, one or more codes for each point in a plane to provide a color-coded vector field image;

detecting, by the detection engine, a lesion indication and a rotor indication by scanning a color-coded vector field image using one or more kernels; and

classifying, by the detection engine, the lesion indication and the trochanter indication as a maintenance lesion.

2. The method of claim 1, wherein the electrocardiographic data signals are detected by a catheter within the anatomy and in communication with the detection engine.

3. The method of claim 1, wherein the detection engine detects one or more segments of the local activation time relative to a first activation time.

4. The method of claim 1, wherein the detection engine models a velocity vector field by: the direction of the electric wave at each x, y point is calculated and the velocity vector field is provided using the derivative of the polynomial surface.

5. The method of claim 1, wherein the detection engine classifies the maintenance foci by utilizing the velocity vector field as an input to a machine learning or artificial intelligence algorithm.

6. The method of claim 5, wherein the machine learning or artificial intelligence algorithm comprises a deep convolutional neural network or a recurrent neural network to detect the location of gold standard maintenance foci in the maintenance foci.

7. The method of claim 5, wherein the machine learning or artificial intelligence algorithm determines whether an ablation result was successful with respect to a particular case of the electrocardiographic data signal.

8. The method of claim 1, wherein the lesion index and the rotor index are detected when all directions are in order within the one or more kernels.

9. The method of claim 1, wherein when marking the foci, the detection engine automatically identifies and annotates atrial fibrillation foci based on vector velocity and ablation information.

10. The method of claim 1, wherein the detection engine uses region of interest annotations with respect to an active category, a passive category, and an unknown category to indicate at least whether a region of interest was ablated or atrial fibrillation termination.

11. A system, comprising:

a memory storing processor executable code for a detection engine; and

at least one processor that executes the processor-executable code to cause the system to:

modeling, by the detection engine, a vector velocity field that measures and quantifies a velocity of the electrocardiographic data signals over a local activation time;

determining, by the detection engine, one or more codes for each point in a plane to provide a color-coded vector field image;

detecting, by the detection engine, a lesion indication and a rotor indication by scanning a color-coded vector field image using one or more kernels; and

classifying, by the detection engine, the lesion indication and the trochanter indication as a maintenance lesion.

12. The system of claim 11, wherein the electrocardiographic data signals are detected by a catheter within the anatomy and in communication with the detection engine.

13. The system of claim 11, wherein the detection engine detects one or more segments of the local activation time relative to a first activation time.

14. The system of claim 11, wherein the detection engine models a velocity vector field by: the direction of the electric wave at each x, y point is calculated and the velocity vector field is provided using the derivative of the polynomial surface.

15. The system of claim 11, wherein the detection engine classifies the maintenance foci by utilizing the velocity vector field as an input to a machine learning or artificial intelligence algorithm.

16. The system of claim 15, wherein the machine learning or artificial intelligence algorithm comprises a deep convolutional neural network or a recurrent neural network to detect the location of gold standard maintenance foci in the maintenance foci.

17. The system of claim 15, wherein the machine learning or artificial intelligence algorithm determines whether an ablation result was successful with respect to a particular case of the electrocardiographic data signal.

18. The system of claim 11, wherein the lesion index and the rotor index are detected when all directions are in order within the one or more kernels.

19. The system of claim 11, wherein the detection engine automatically identifies and annotates atrial fibrillation foci based on vector velocity and ablation information when marking the foci.

20. The system of claim 11, wherein the detection engine uses region of interest annotations with respect to an active category, a passive category, and an unknown category to indicate at least whether a region of interest was ablated or atrial fibrillation termination.

Technical Field

The present invention relates to artificial intelligence and machine learning associated with atrial fibrillation. More particularly, the present invention relates to systems and methods for implementing machine learning/artificial intelligence algorithms for detecting atrial fibrillation and termination of atrial fibrillation.

Background

Atrial fibrillation ("aFib") is a tremor or irregular heartbeat (arrhythmia) that can lead to blood clots, stroke, heart failure, and other heart related complications. aFib is the most common arrhythmia diagnosed in clinical practice. Estimates of the prevalence of aFib in the united states range from about 2.7 to 6.1 million, and is expected to rise to 12.1 million in 2030. According to the 2013 study, the global estimate estimates the number of individuals with aFib in 2010 to be about 33.5 million. This accounts for about 0.5% of the world population.

Currently, physicians are unable to successfully determine whether and when a particular aFib case terminates based on a set of Electrocardiogram (ECG) signals. For example, conventional mechanisms discuss phase mapping (i.e., calculating delays between electrodes and finding phase singularities) and vector analysis without using velocity vector fields, machine learning, deep learning, and/or other detailed algorithms. Most preferably, conventional mechanisms may use the velocity characteristics of the aFib source determined by electrogram flow mapping before and after catheter ablation, yet these conventional mechanisms still fail to distinguish between active and passive lesion sources. In turn, conventional mechanisms fail to determine that the aFib terminates.

Disclosure of Invention

According to one exemplary embodiment, a method is provided. The method is implemented by a detection engine embodied in processor-executable code stored on a memory and executed by at least one processor. The method includes modeling a vector velocity field that measures and quantifies the velocity of the electrocardiographic data signal over a local activation time. The method further comprises the following steps: determining one or more codes for each point in the plane to provide a color-coded vector field image; detecting a lesion indication and a rotor indication by scanning the color-coded vector field image using one or more kernels; and classifying the lesion indication and the rotor indication as a maintenance lesion.

In accordance with one or more embodiments, the above-described exemplary method embodiments can be implemented as an apparatus, system, and/or computer program product.

Drawings

A more particular understanding can be obtained by reference to the following detailed description, which is provided by way of example in connection with the accompanying drawings, wherein like reference numbers refer to like elements, and in which:

fig. 1 is an illustration of an exemplary system in which one or more features of the disclosed subject matter may be implemented.

FIG. 2 shows a block diagram of an exemplary system for anatomically correct reconstruction of an atrium according to one or more embodiments;

FIG. 3 illustrates a method in accordance with one or more embodiments;

FIG. 4 depicts a graphical depiction of an artificial intelligence system in accordance with one or more illustrative embodiments;

fig. 5 illustrates an example of a block diagram of a neural network and a method performed in the neural network in accordance with one or more embodiments;

FIG. 6 illustrates a method in accordance with one or more embodiments;

fig. 7 shows a graph in accordance with one or more embodiments;

FIG. 8 shows a graph of a surface (x, y) according to one or more embodiments; and is

Fig. 9 illustrates a graph of a velocity vector field of the surface (x, y) of fig. 8, according to one or more embodiments.

Detailed Description

Machine learning and/or artificial intelligence methods and systems implemented by a detection engine are disclosed herein. More particularly, the present invention relates to a detection engine that includes a machine learning/artificial intelligence algorithm that detects aFib and aFib termination.

One or more advantages, technical effects, and/or benefits of the detection engine may include using a feedback loop based on actual ablation of lesion activity to address active and passive issues (e.g., to distinguish between lesion source and rotor), otherwise not obtainable by conventional mechanisms. In this regard, the detection engine may model the vector velocity field while distinguishing between the source of the lesion and the rotor (e.g., active and passive). That is, the detection engine may define a location to calculate a Local Activation Time (LAT), calculate a derivative of the LAT to obtain a velocity, identify a focal source (e.g., within a 1mm box), classify an active focal source or a passive focal source (e.g., in a 1mm box), provide retrospective analysis (e.g., investigate past cases and determine where ablation occurred), and provide prospective analysis (e.g., determine where to ablate).

For ease of explanation, the detection engine is described herein with respect to determining and treating aFib with respect to the heart; however, any anatomical structure, body part, organ, or portion thereof may be a target for mapping by the detection engine described herein. Additionally, the detection engine and/or the machine learning/artificial intelligence algorithm are processor executable code or software that must be rooted in the processing operations of the medical device equipment and its processing hardware.

In accordance with one or more embodiments, a method is provided that is implemented by a detection engine embodied in processor-executable code stored on a memory and executed by at least one processor. The method includes modeling, by the detection engine, a vector velocity field that measures and quantifies a velocity of the electrocardiographic data signal over a local activation time; determining, by the detection engine, one or more codes for each point in a plane to provide a color-coded vector field image; detecting, by the detection engine, a lesion indication and a rotor indication by scanning the color-coded vector field image using one or more kernels; and classifying, by the detection engine, the lesion indication and the trochanter indication as a maintenance lesion.

According to one or more embodiments or any of the method embodiments herein, the electrocardiogram data signal may be detected by a catheter within the anatomy and in communication with the detection engine.

According to one or more embodiments or any of the method embodiments herein, the detection engine may detect one or more segments of the local activation time relative to a first activation time.

According to one or more embodiments or any of the method embodiments herein, the detection engine may model the velocity vector field by: the direction of the electric wave at each x, y point is calculated and the velocity vector field is provided using the derivative of the polynomial surface.

According to one or more embodiments or any of the method embodiments herein, the detection engine may classify the maintenance foci by utilizing the velocity vector field as an input to a machine learning or artificial intelligence algorithm.

According to one or more embodiments or any of the method embodiments herein, the machine learning or artificial intelligence algorithm may comprise a deep convolutional or recurrent neural network to detect the location of gold standard maintenance foci in the maintenance foci.

According to one or more embodiments or any of the method embodiments herein, the machine learning or artificial intelligence algorithm may determine whether ablation results are successful for a particular case of the electrocardiographic data signal.

According to one or more embodiments or any of the method embodiments herein, the lesion index and the trochanter index are detectable when all directions are sequential within the one or more kernels.

According to one or more embodiments or any of the method embodiments herein, when marking the maintenance foci, the detection engine automatically identifies and annotates atrial fibrillation maintenance foci based on vector velocity and ablation information.

According to one or more embodiments or any of the method embodiments herein, the detection engine may use region of interest annotations with respect to the active category, the passive category, and the unknown category to indicate at least whether to ablate the region of interest or terminate atrial fibrillation.

According to one or more embodiments, a system includes a memory storing processor executable code for a detection engine. The system also includes at least one processor that executes the processor executable code to cause the system to: modeling, by the detection engine, a vector velocity field that measures and quantifies a velocity of the electrocardiographic data signals over a local activation time; determining, by the detection engine, one or more codes for each point in a plane to provide a color-coded vector field image; detecting, by the detection engine, a lesion indication and a rotor indication by scanning the color-coded vector field image using one or more kernels; and classifying, by the detection engine, the lesion indication and the trochanter indication as a maintenance lesion.

According to one or more embodiments or any of the system embodiments herein, the electrocardiogram data signal is detectable by a catheter within the anatomy and in communication with the detection engine.

According to one or more embodiments or any of the system embodiments herein, the detection engine may detect one or more segments of the local activation time relative to a first activation time.

According to one or more embodiments or any of the system embodiments herein, the detection engine may model the velocity vector field by: the direction of the electric wave at each x, y point is calculated and the velocity vector field is provided using the derivative of the polynomial surface.

According to one or more embodiments or any of the system embodiments herein, the detection engine may classify the maintenance foci by utilizing the velocity vector field as an input to a machine learning or artificial intelligence algorithm.

According to one or more embodiments or any of the system embodiments herein, the machine learning or artificial intelligence algorithm may comprise a deep convolutional or recurrent neural network to detect the location of gold standard maintenance foci in the maintenance foci.

According to one or more embodiments or any of the system embodiments herein, the machine learning or artificial intelligence algorithm may determine whether ablation results are successful with respect to a particular case of the electrocardiographic data signal.

According to any of one or more embodiments or system embodiments herein, the lesion index and the trochanter index are detectable when all directions are sequential within the one or more kernels.

According to any of the one or more embodiments or system embodiments herein, when the maintenance foci are marked, the detection engine automatically identifies and annotates atrial fibrillation maintenance foci based on vector velocity and ablation information.

In accordance with one or more embodiments or any of the system embodiments herein, the detection engine may use region of interest annotations with respect to the active category, the passive category, and the unknown category to indicate at least whether to ablate the region of interest or terminate atrial fibrillation.

Fig. 1 is a diagram of an exemplary system (e.g., medical device equipment), shown as system 100, in which one or more features of the subject matter herein may be implemented according to one or more embodiments. All or portions of the system 100 may be used to collect information (e.g., biometric data and/or training data sets) and/or to implement the detection engine 101 (e.g., machine learning and/or artificial intelligence algorithms), as described herein. The detection engine 101 may be defined as a deep learning optimization for detecting a maintenance focus of the aFib to be ablated to treat a persistent aFib subject and classify the velocity vector field images and raw data into maintenance focuses.

As shown, the system 100 includes a probe 105 having a catheter 110 (including at least one electrode 111), a shaft 112, a sheath 113, and a manipulator 114. As shown, the system 100 also includes a physician 115 (or medical professional or clinician), a heart 120, a patient 125, and a bed 130 (or table). Note that illustrations 140 and 150 show heart 120 and catheter 110 in more detail. As shown, the system 100 also includes a console 160 (including one or more processors 161 and memory 162) and a display 165. It is also noted that each element and/or item of system 100 represents one or more of that element and/or that item. The example of the system 100 shown in fig. 1 may be modified to implement the embodiments disclosed herein. The disclosed embodiments of the invention may be similarly applied using other system components and arrangements. Additionally, the system 100 may include additional components, such as elements for sensing electrical activity, wired or wireless connectors, processing and display devices, and the like.

The system 100 may be used to detect, diagnose, and/or treat a cardiac disorder (e.g., using the monitoring engine 101). Cardiac disorders such as cardiac arrhythmias have long been a common and dangerous medical condition, especially among the elderly. Additionally, the system 100 may be a surgical system (e.g., sold by Biosense Webster)A system) configured to obtain biometric data (e.g., anatomical and electrical measurements of a patient organ, such as the heart 120) and perform a cardiac ablation procedure.More specifically, treatment of cardiac disorders such as arrhythmias often requires obtaining a detailed map of the cardiac tissue, chambers, veins, arteries, and/or electrical pathways. For example, a prerequisite to successful catheter ablation (as described herein) is that the cause of the arrhythmia is accurately located in the chamber of the heart 120. Such localization may be accomplished via electrophysiological studies during which electrical potentials are spatially resolved detected with a mapping catheter (e.g., catheter 110) introduced into a chamber of the heart 120. This electrophysiological study (so-called electroanatomical mapping) thus provides 3D mapping data that can be displayed on a monitor. In many cases, mapping and treatment functions (e.g., ablation) are provided by a single catheter or a set of catheters, such that the mapping catheter also operates simultaneously as a treatment (e.g., ablation) catheter. In this case, detection engine 101 may be stored and executed directly by catheter 110.

In a patient (e.g., patient 125) with a Normal Sinus Rhythm (NSR), a heart (e.g., heart 120) including atria, ventricles, and excitatory conducting tissue is electrically stimulated to beat in a synchronized, patterned manner. It is noted that the electrical stimulation may be detected as intracardiac electrocardiogram (IC ECG) data or the like.

Generally, the heart 120 is made up of four chambers-two upper chambers (atria) and two lower chambers (ventricles). The Coronary Sinus (CS) is a collection of veins that join together to form the great vessels that collect blood from the myocardium and deliver less oxygenated blood to the right atrium. The rhythm of the heart 120 is typically controlled by a sinoatrial node (not shown) located in the right atrium. The sinoatrial node produces an electrical pulse that typically begins at each heart beat and acts as a natural pacemaker. An electrical pulse travels from the sinoatrial node through the atrium, causing the atrial muscle to contract and pump blood into the ventricle. The electrical impulses then arrive at a cluster of cells called the atrioventricular node (AV node) (not shown). The AV node is typically the only path for a signal to travel from the atria to the ventricles. The AV node slows the electrical signal before sending it to the ventricles. Delaying, if at all slightly, allows the ventricles to fill with blood. When the electrical pulse reaches the muscles of the ventricles, the muscles contract, causing the muscles to pump blood to the lungs or the rest of the body. In a healthy heart 120, the process is generally smooth, resulting in a normal resting heart rate of 60 to 100 beats/minute. In the heart 120 having one of the above identified disease states, abnormal regions of faulty electrical connections or electrical activity in the heart trigger and maintain abnormal rhythms. When this occurs, the heart rate accelerates too quickly and does not allow sufficient time for the heart 120 to fill before it contracts again. These ineffective contractions of the heart 120 can cause mild dizziness or stun because the brain may not receive sufficient blood and oxygen.

In patients (e.g., patient 125) with arrhythmias (e.g., atrial fibrillation or aFib), abnormal regions of cardiac tissue do not follow the synchronous beat cycles associated with normal conducting tissue, in contrast to patients with NSR. In contrast, abnormal regions of cardiac tissue are abnormally conducted to adjacent tissue, thereby disrupting the cardiac cycle to an asynchronous rhythm. Note that this asynchronous rhythm may also be detected as IC ECG data. Such abnormal conduction is previously known to occur in various regions of the heart 120, such as in the Sinoatrial (SA) junction region, along the conduction pathway of the Atrioventricular (AV) node, or in the myocardial tissue forming the walls of the ventricular and atrial heart chambers. Other conditions exist (such as tremor) in which a pattern of abnormal conductive tissue causes reentry paths such that the chamber beats in a regular pattern, which may be a multiple of the sinus rhythm.

To support the system 100 in detecting, diagnosing, and/or treating cardiac conditions, the probe 105 may be navigated by a physician 115 into the heart 120 of a patient 125 lying in a bed 130. For example, the physician 115 may insert the shaft 112 through the sheath 113 while manipulating the distal end of the shaft 112 using a manipulator 114 near the proximal end of the catheter 110 and/or deflecting from the sheath 113. As shown in inset 140, basket catheter 110 may be fitted at the distal end of shaft 112. Basket catheter 110 may be inserted through sheath 113 in a collapsed state and then may be deployed within heart 120.

In general, the electrical activity at a point in the heart 120 may be measured by advancing a catheter 110 containing an electrical sensor (e.g., at least one electrode 111) at or near its distal tip to the point in the heart 120, contacting the tissue with the sensor and acquiring data at the point. One disadvantage of using a catheter containing only a single distal tip electrode to map a heart chamber is the long time required to acquire data point-by-point over the necessary number of points required for a detailed map of the chamber population. Accordingly, multi-electrode catheters (e.g., catheter 110) have been developed to measure electrical activity at multiple points in the heart chamber simultaneously.

The catheter 110, which may include at least one electrode 111 and a catheter needle coupled to its body, may be configured to obtain biometric data, such as electrical signals of an internal organ (e.g., the heart 120) and/or ablate a tissue region thereof (e.g., a heart chamber of the heart 120). Note that electrode 111 represents any similar element, such as a tracking coil, a piezoelectric transducer, an electrode, or a combination of elements configured to ablate a tissue region or obtain biometric data. According to one or more embodiments, catheter 110 may include one or more position sensors for determining trajectory information. Trajectory information can be used to infer motion characteristics, such as the contractility of tissue.

The biometric data (e.g., patient biometric, patient data, or patient biometric data) may include one or more of Local Activation Time (LAT), electrical activity, topology, bipolar mapping, reference activity, ventricular activity, dominant frequency, impedance, etc. The LAT may be a point in time corresponding to a locally activated threshold activity calculated based on a normalized initial starting point. The electrical activity may be any suitable electrical signal that may be measured based on one or more thresholds and may be sensed and/or enhanced based on a signal-to-noise ratio and/or other filters. The topology may correspond to the physical structure of a body part or a portion of a body part, and may correspond to a change in the physical structure relative to a different portion of the body part or relative to a different body part. The dominant frequency may be a frequency or range of frequencies that are ubiquitous at one part of the body part and may be different in different parts of the same body part. For example, the dominant frequency of the PV of a heart may be different from the dominant frequency of the right atrium of the same heart. The impedance may be a measure of the electrical resistance at a given region of the body part.

Examples of biometric data include, but are not limited to, patient identification data, IC ECG data, bipolar intracardiac reference signals, anatomical and electrical measurements, trajectory information, Body Surface (BS) ECG data, historical data, brain biometrics, blood pressure data, ultrasound signals, radio signals, audio signals, two or three dimensional image data, blood glucose data, and temperature data. Biometric data can generally be used in order to monitor, diagnose, and treat any number of a variety of diseases, such as cardiovascular diseases (e.g., arrhythmias, cardiomyopathy, and coronary artery disease) and autoimmune diseases (e.g., type I and type II diabetes). Note that BS ECG data may include data and signals collected from electrodes on the surface of a patient, IC ECG data may include data and signals collected from electrodes within the patient, and ablation data may include data and signals collected from tissue that has been ablated. In addition, BS ECG data, IC ECG data, and ablation data along with catheter electrode position data may be derived from one or more protocol recordings.

For example, the catheter 110 may use the electrodes 111 to enable intravascular ultrasound and/or MRI catheterization to image (e.g., obtain and process biometric data) the heart 120. Inset 150 shows catheter 110 in an enlarged view within a heart chamber of heart 120. Although the catheter 110 is shown as a tip catheter, it should be understood that any shape including one or more electrodes 111 may be used to implement the exemplary embodiments disclosed herein.

Examples of catheter 110 include, but are not limited to, a linear catheter with multiple electrodes, a balloon catheter including electrodes dispersed over multiple ridges that shape the balloon, a lasso or loop catheter with multiple electrodes, a contact force sensing catheter, or any other suitable shape or type. The linear catheter may be fully or partially elastic such that it may twist, bend, and/or otherwise change its shape based on the received signals and/or based on the application of an external force (e.g., cardiac tissue) on the linear catheter. Balloon catheters can be designed such that when deployed into a patient, their electrodes can remain in intimate contact against the endocardial surface. For example, a balloon catheter may be inserted into a lumen, such as a PV. The balloon catheter may be inserted into the PV in a deflated state such that the balloon catheter does not occupy its maximum volume when inserted into the PV. The balloon catheter may be inflated inside the PV such that those electrodes on the balloon catheter are in contact with the entire circular segment of the PV. Such contact with the entire circular section of the PV or any other lumen may enable effective imaging and/or ablation.

According to other examples, the body patches and/or body surface electrodes may also be positioned on or near the body of the patient 125. A catheter 110 having one or more electrodes 111 may be positioned within the body (e.g., within the heart 120), and the position of the catheter 110 may be determined by the system 100 based on signals transmitted and received between the one or more electrodes 111 of the catheter 110 and body patches and/or body surface electrodes. In addition, the electrodes 111 may sense biometric data from within the patient 125, such as within the heart 120 (e.g., the electrodes 111 sense the electrical potential of tissue in real time). The biometric data may be associated with the determined position of catheter 110 such that a rendering of a body part of the patient (e.g., heart 120) may be displayed and the biometric data overlaid on the body part shape may be displayed.

The probe 105 and other items of the system 100 may be connected to a console 160. The console 160 may include any computing device that employs machine learning and/or artificial intelligence algorithms, represented as detection engines 101. According to an exemplary embodiment, the console 160 includes one or more processors 161 (any computing hardware) and memory 162 (any non-transitory tangible medium), wherein the one or more processors 161 execute computer instructions with respect to the detection engine 101 and the memory 162 stores the instructions for execution by the one or more processors 161. For example, the console 160 may be configured to receive and process biometric data and determine whether a given tissue region is conductive.

In some embodiments, the console 160 may also be programmed (in software) by the detection engine 101 to perform the following functions: modeling a vector velocity field that measures and quantifies the velocity of the electrocardiographic data signals over the local activation time; determining one or more codes for each point in the plane to provide a color-coded vector field image; detecting a lesion indication and a rotor indication by scanning the color-coded vector field image using one or more kernels (e.g., a space within a map); and classifying the lesion indication and the rotor indication as a maintenance lesion. For example, the detection engine 101 may include a deep learning optimization (described herein with respect to fig. 3 and 6) that receives biometric data acquired by the catheter 110 as the catheter is maneuvered within the anatomy. Once the mapping is generated, the detection engine 101 may receive input representing user modifications of the mapping, such as through an existing user interface and/or a dedicated user interface of the detection engine 101. In general, the detection engine 101 can provide one or more user interfaces, such as on behalf of an operating system or other application and/or directly as desired. The user interface includes, but is not limited to, an internet browser, a Graphical User Interface (GUI), a windows interface, and/or other visual interfaces for applications, operating systems, folders, and the like. In accordance with one or more embodiments, detection engine 101 may be located external to console 160, and may be located, for example, in conduit 110, in an external device, in a mobile device, in a cloud-based device, or may be a stand-alone processor. In this regard, the detection engine 101 may be transmitted/downloaded over a network in electronic form.

In one example, the console 160 may be any computing device (such as a general purpose computer) as described herein including software (e.g., the detection engine 101) and/or hardware (e.g., the processor 161 and the memory 162) with suitable front end and interface circuitry for transmitting and receiving signals to and from the probe 105, as well as for controlling other components of the system 100. For example, the front end and interface circuitry includes an input/output (I/O) communication interface that enables the console 160 to receive signals from and/or transmit signals to the at least one electrode 111. The console 160 may include real-time noise reduction circuitry, typically configured as a Field Programmable Gate Array (FPGA), followed by an analog-to-digital (a/D) ECG or electrocardiograph or Electromyography (EMG) signal conversion integrated circuit. The console 160 may transfer signals from the a/D ECG or EMG circuitry to another processor and/or may be programmed to perform one or more of the functions disclosed herein.

The display 165 may be any electronic device for visual presentation of biometric data, which is connected to the console 160. According to an exemplary embodiment, during a procedure, console 160 may facilitate presentation of body part renderings to physician 115 on display 165 and storing data representing the body part renderings in memory 162. For example, a map depicting motion characteristics may be rendered/constructed based on trajectory information sampled at a sufficient number of points in the heart 120. By way of example, display 165 may include a touch screen that may be configured to accept input from medical professional 115 in addition to presenting body part renderings.

In some embodiments, the physician 115 may manipulate the elements of the system 100 and/or the body part rendering using one or more input devices (such as a touchpad, a mouse, a keyboard, a gesture recognition device, etc.). For example, an input device may be used to change the position of catheter 110 so that the rendering is updated. It is noted that the display 165 may be located at the same location or at a remote location, such as in a separate hospital or a separate healthcare provider network.

According to one or more embodiments, the system 100 may also obtain biometric data using ultrasound, Computed Tomography (CT), MRI, or other medical imaging techniques utilizing the catheter 110 or other medical equipment. For example, the system 100 may use one or more catheters 110 or other sensors to obtain ECG data and/or anatomical and electrical measurements (e.g., biometric data) of the heart 120. More specifically, the console 160 may be connected by a cable to a BS electrode that includes an adhesive skin patch that is attached to the patient 125. The BS electrodes may obtain/generate biometric data in the form of BS ECG data. For example, processor 161 may determine position coordinates of catheter 110 within a body part of patient 125 (e.g., heart 120). The position coordinates may be based on impedance or electromagnetic fields measured between the body surface electrodes and the electrodes 111 or other electromagnetic components of the catheter 110. Additionally or alternatively, a location pad that generates a magnetic field for navigation may be located on the surface of the bed 130 and may be separate from the bed 130. The biometric data may be transmitted to the console 160 and stored in the memory 162. Alternatively or in addition, the biometric data may be transmitted to a server 1760, which may be local or remote, using a network 1762.

According to one or more exemplary embodiments, the catheter 110 may be configured to ablate a tissue region of a heart chamber of the heart 120. Inset 150 shows catheter 110 in an enlarged view within a heart chamber of heart 120. For example, an ablation electrode, such as at least one electrode 111, may be configured to provide energy to a tissue region of an internal body organ (e.g., heart 120). The energy may be thermal energy and may cause damage to the tissue region starting at a surface of the tissue region and extending into a thickness of the tissue region. Biometric data relative to an ablation procedure (e.g., ablating tissue, ablating location, etc.) can be considered ablation data.

According to one example, a multi-electrode catheter (e.g., catheter 110) may be advanced into a chamber of heart 120 relative to obtaining biometric data. Anteroposterior (AP) and lateral fluorescence maps can be obtained to establish the position and orientation of each electrode. An ECG may be recorded from each of the electrodes 111 in contact with the surface of the heart relative to a time reference, such as the onset of a P-wave in the sinus rhythm of the BS ECG and/or a signal from the electrode 111 of the catheter 110 placed in the coronary sinus. As further disclosed herein, the system can distinguish between those electrodes that record electrical activity and those electrodes that do not record electrical activity due to not being in close proximity to the endocardial wall. After recording the initial ECG, the catheter can be repositioned and the fluoroscopic image and ECG can be recorded again. An electrical map may then be constructed (e.g., via cardiac mapping) according to an iteration of the above-described process.

Cardiac mapping may be accomplished using one or more techniques. In general, mapping of cardiac regions such as cardiac regions, tissue, veins, arteries, and/or electrical pathways of the heart 120 may result in identifying problem areas such as scar tissue, sources of arrhythmia (e.g., electrical rotors), healthy areas, and the like. The cardiac region may be mapped such that a visual rendering of the mapped cardiac region is provided using a display, as further disclosed herein. Additionally, cardiac mapping (which is an example of cardiac imaging) may include mapping based on one or more modalities such as, but not limited to, LAT, local activation velocity, electrical activity, topology, bipolar maps, dominant frequency, or impedance. Data (e.g., biometric data) corresponding to multiple modalities may be captured using a catheter (e.g., catheter 110) inserted into a patient and may be provided for rendering simultaneously or at different times based on corresponding settings and/or preferences of physician 115.

As an example of the first technique, cardiac mapping may be accomplished by sensing electrical properties (e.g., LAT) of cardiac tissue from precise locations within the heart 120. Corresponding data (e.g., biometric data) may be acquired by one or more catheters (e.g., catheter 110) advanced into the heart 1120 and having electrical and position sensors (e.g., electrodes 111) in its distal tip. As a specific example, the location and electrical activity may be initially measured at about 10 to about 20 points on the inner surface of the heart 120. These data points may generally be sufficient to generate a satisfactory quality preliminary reconstruction or map of the cardiac surface. The preliminary map may be combined with data taken at additional points in order to produce a more comprehensive map of cardiac electrical activity. In a clinical setting, it is not uncommon to accumulate data at 100 or more sites (e.g., thousands) to generate a detailed and comprehensive map of the heart chamber electrical activity. The detailed map generated can then be used as a basis for deciding on the course of therapeutic action, such as tissue ablation as described herein, to alter the propagation of cardiac electrical activity and restore a normal heart rhythm.

Additionally, a cardiac map may be generated based on the detection of intracardiac potential fields (e.g., which are examples of IC ECG data and/or bipolar intracardiac reference signals). Non-contact techniques for simultaneously acquiring large amounts of electrical information of the heart may be implemented. For example, a catheter type having a distal end portion may be provided with a series of sensor electrodes distributed over its surface and connected to insulated electrical conductors for connection to a signal sensing and processing device. The end portion may be sized and shaped such that the electrode is substantially spaced from the wall of the heart chamber. The intracardiac potential field may be detected during a single heartbeat. According to one example, the sensor electrodes may be distributed over a series of circumferences lying in planes spaced apart from each other. These planes may be perpendicular to the long axis of the end portion of the catheter. At least two additional electrodes may be provided adjacent at the ends of the long axis of the end. As a more specific example, the catheter may include four circumferences, with eight electrodes equiangularly spaced on each circumference. Thus, in this implementation, the catheter may include at least 34 electrodes (32 circumferential electrodes and 2 end electrodes). As another more specific example, the catheter may include other multi-splined catheters, such as five soft flexible branches, eight radial splines, or a parallel spline scoop type (e.g., any of which may have a total of 42 electrodes).

As an example of electrical or cardiac mapping, electrophysiology cardiac mapping systems and techniques based on non-contact and non-expanding multi-electrode catheters (e.g., catheter 110) may be implemented. An ECG may be obtained with one or more catheters 110 having multiple electrodes (e.g., such as between 42-122 electrodes). According to this implementation, knowledge of the relative geometry of the probe and endocardium can be obtained by a separate imaging modality, such as transesophageal echocardiography. After independent imaging, the non-contact electrodes may be used to measure cardiac surface potentials and construct a map therefrom (e.g., using bipolar intracardiac reference signals in some cases). The technique may include the following steps (after the separate imaging step): (a) measuring electrical potentials with a plurality of electrodes disposed on a probe positioned in heart 120; (b) determining the geometric relationship of the probe surface and the endocardial surface and/or other references; (c) generating a coefficient matrix representing a geometric relationship of the probe surface and the endocardial surface; and (d) determining the endocardial potential based on the electrode potential and the coefficient matrix.

According to another example of electrical or cardiac mapping, techniques and devices for mapping the electrical potential distribution of a heart chamber may be implemented. An intracardiac multi-electrode mapping catheter assembly may be inserted into the heart 120. A mapping catheter (e.g., catheter 110) assembly may include a multi-electrode array or mating reference catheter with one or more integral reference electrodes (e.g., one or more electrodes 111).

According to one or more exemplary embodiments, the electrodes may be deployed in a substantially spherical array that may be spatially referenced to a point on the endocardial surface by a reference electrode or by a reference catheter in contact with the endocardial surface. Preferred electrode array catheters can carry a plurality of individual electrode sites (e.g., at least 24). In addition, the exemplary technique can be implemented by knowing the location of each of the electrode sites on the array and knowing the geometry of the heart. These locations are preferably determined by the technique of impedance plethysmography.

In view of electrical or cardiac mapping and according to another example, the catheter 110 may be a cardiac mapping catheter assembly, which may include an electrode array defining a plurality of electrode sites. The cardiac mapping catheter assembly may also include a lumen to receive a reference catheter having a distal tip electrode assembly that may be used to probe the heart wall. A cardiac mapping catheter assembly may include a braid of insulated wires (e.g., 24 to 64 wires in the braid), and each wire may be used to form an electrode site. The cardiac mapping catheter assembly may be readily positioned in the heart 120 for acquiring electrical activity information from the first set of non-contact electrode sites and/or the second set of contact electrode sites.

Furthermore, according to another example, the catheter 110, which may enable mapping electrophysiological activity within the heart, may comprise a distal tip adapted to deliver stimulation pulses for pacing the heart or an ablation electrode for ablating tissue in contact with the tip. The catheter 110 may also include at least one pair of orthogonal electrodes to generate a difference signal indicative of local cardiac electrical activity of adjacent orthogonal electrodes.

As described herein, the system 100 may be used to detect, diagnose, and/or treat cardiac disorders. In an exemplary operation, a process for measuring electrophysiological data in a heart chamber may be implemented by the system 100. The process may include, in part, positioning a set of active and passive electrodes into the heart 120, supplying current to the active electrodes, thereby generating an electric field in the heart chamber, and measuring the electric field at the location of the passive electrodes. The passive electrodes are included in an array positioned on an inflatable balloon of the balloon catheter. In a preferred embodiment, the array is said to have 60 to 64 electrodes.

As another exemplary operation, cardiac mapping may be accomplished by the system 100 using one or more ultrasound transducers. An ultrasound transducer may be inserted into a patient's heart 120 and a plurality of ultrasound slices (e.g., two-dimensional or three-dimensional slices) may be collected at various locations and orientations within the heart 120. The position and orientation of a given ultrasound transducer may be known, and the collected ultrasound slices may be stored so that they may be displayed at a later time. One or more ultrasound slices corresponding to the position of the probe 105 (e.g., a treatment catheter shown as catheter 110) at a later time may be displayed, and the probe 105 may overlay the one or more ultrasound slices.

In view of system 100, it is noted that arrhythmias, including atrial arrhythmias, may be of the multi-wavelet reentrant type characterized by multiple asynchronous loops of electrical impulses dispersed around the atrial chamber and generally self-propagating (e.g., another example of IC ECG data). Alternatively, or in addition to the multi-wavelet reentry type, the arrhythmia may also have a focal source (e.g., another example of IC ECG data), such as when an isolated tissue region within the atrium beats autonomously in a fast repeating manner. Ventricular tachycardia (V-tach or VT) is a tachycardia or tachyarrhythmia that originates in one of the ventricles. This is a potentially life-threatening arrhythmia, as it can lead to ventricular fibrillation and sudden death.

For example, aFib occurs when normal electrical impulses generated by the sinoatrial node (e.g., another example of IC ECG data) are overwhelmed by disorganized electrical impulses originating from the atrial veins and PV that cause irregular impulses to be transmitted to the ventricles. Irregular heartbeats occur and may last from minutes to weeks, or even years. aFib is often a chronic condition with a small increase in the risk of death, usually due to stroke. Line therapy for aFib is a medication that slows down or normalizes the heart rhythm. Additionally, people with aFib are often given anticoagulants to prevent them from being at risk of stroke. The use of such anticoagulants is associated with its own risk of internal bleeding. For some patients, drug therapy is inadequate, and their aFib is considered drug refractory, i.e. no treatment is available with standard drug intervention. Synchronous electrical cardioversion may also be used to transition aFib to a normal heart rhythm. Alternatively, aFib patients are treated by catheter ablation.

Catheter ablation-based treatments may include mapping electrical properties of cardiac tissue (particularly endocardium and heart volume), and selectively ablating the cardiac tissue by applying energy. Electrical or cardiac mapping (e.g., implemented by any of the electrophysiology cardiac mapping systems and techniques described herein) includes creating a map of electrical potentials propagating along waves of cardiac tissue (e.g., a voltage map) or a map of arrival times to various tissue locations (e.g., a LAT map). Electrical or cardiac mapping (e.g., cardiac maps) may be used to detect local cardiac tissue dysfunction. Ablation, such as ablation based on cardiac mapping, may stop or alter the propagation of unwanted electrical signals from one portion of the heart 120 to another.

The ablation process damages the unwanted electrical pathways by forming electrically non-conductive lesions. Various forms of energy delivery for forming lesions have been disclosed and include the use of microwaves, lasers and more commonly radio frequency energy to form conduction blocks along the walls of cardiac tissue. Another example of an energy delivery technique includes irreversible electroporation (IRE), which provides a high electric field that damages cell membranes. In a two-step procedure (e.g., mapping followed by ablation), electrical activity at various points within the heart 120 is typically sensed and measured by advancing a catheter 110 containing one or more electrical sensors (or electrodes 111) into the heart 120 and obtaining/acquiring data at the various points (e.g., generally as biometric data, or specifically as ECG data). The ECG data is then used to select an endocardial target area where ablation is to be performed.

Cardiac ablation and other cardiac electrophysiology protocols become increasingly complex as clinicians treat increasingly challenging conditions such as atrial fibrillation and ventricular tachycardia. Treatment of complex arrhythmias may rely solely on the use of a three-dimensional (3D) mapping system in order to reconstruct the anatomy of the heart chamber of interest. In this regard, the detection engine 101 employed by the system 100 herein generally manipulates and evaluates biometric data or specifically ECG dataTo generate improved tissue data that enables more accurate diagnosis, imaging, scanning, and/or mapping for treating abnormal heartbeats or arrhythmias. For example, cardiologists rely on software, such as that produced by Biosense Webster, Inc. (Diamond Bar, Calif.)A Complex Fractionated Atrial Electrogram (CFAE) module of the 33D mapping system to generate and analyze ECG data. The detection engine 101 of the system 100 enhances the software to generate and analyze improved biometric data, which further provides a plurality of pieces of information about the electrophysiological properties of the heart 120 (including scar tissue) that are representative of the cardiac matrix (anatomy and function) of the aFib.

Thus, the system 100 may implement a 3D mapping system such asA 33D mapping system to locate potential arrhythmogenic substrates of cardiomyopathy in terms of abnormal EGM detection. The stroma associated with these cardiac conditions is associated with the presence of fragmented and prolonged ECGs in the endocardial and/or epicardial layers of the ventricular chambers (right and left). For example, areas of low or medium voltage may exhibit ECG fragmentation and prolonged activity. Furthermore, during sinus rhythm, regions of low or medium voltage may correspond to key isthmuses identified during persistent and organized ventricular arrhythmias (e.g., applicable to intolerant ventricular tachycardia, as well as in the atrium). In general, abnormal tissue is characterized by a low voltage ECG. However, initial clinical experience in intracardiac-epicardial mapping indicates that the low voltage region is not always present as the only arrhythmogenic mechanism in such patients. Indeed, regions of low or medium voltage may exhibit EGM fragmentation and prolonged activity during sinus rhythms corresponding to critical isthmuses identified during persistent and tissue ventricular arrhythmias, e.g., applicable only to intolerant ventricular tachycardias. Furthermore, in many cases, the voltage amplitude is at or near normal (>1-1.5mV) of the EGM in the regionAnd (6) moving. While a region can then be evaluated in terms of voltage amplitude, they cannot be considered normal in terms of intracardiac signals, and thus represent a true arrhythmogenic substrate. The 3D mapping can localize the proarrhythmic matrix on the endocardial and/or epicardial layers of the right/left ventricle, which can vary in distribution according to the spread of the primary disease.

As another exemplary operation, cardiac mapping may be accomplished by the system 100 using one or more multi-electrode catheters (e.g., catheter 110). Multi-electrode catheters are used to stimulate and map electrical activity in the heart 120 and to ablate sites of abnormal electrical activity. In use, a multi-electrode catheter is inserted into a major vein or artery, such as the femoral vein, and then directed into a chamber of the heart 120 of interest. A typical ablation procedure involves inserting a catheter 110 having at least one electrode 111 at its distal end into a heart chamber. A reference electrode glued to the skin of the patient is provided, or provided by a second catheter positioned in or near the heart or selected from one or other electrodes 111 of the catheter 110. Radio Frequency (RF) current is applied to the tip electrode 111 of the ablation catheter 110, and the current flows to the reference electrode through the medium (e.g., blood and tissue) surrounding it. The distribution of the current depends on the amount of contact of the electrode surface with the tissue compared to blood, which has a higher conductivity than the tissue. Heating of the tissue occurs due to the electrical resistance of the tissue. The tissue is heated sufficiently to cause cell destruction in the heart tissue, resulting in the formation of non-conductive foci within the heart tissue. In this process, heating of the tip electrode 111 also occurs due to conduction from the heated tissue to the electrode itself. If the electrode temperature becomes high enough, possibly above 60 ℃, a thin transparent coating of dehydrated blood proteins can form on the surface of the electrode 111. If the temperature continues to rise, the dehydrated layer may become thicker, resulting in blood clotting on the electrode surface. Because dehydrated biological material has a higher electrical resistance than endocardial tissue, the impedance to the flow of electrical energy into the tissue also increases. If the impedance increases sufficiently, an impedance rise occurs and the catheter 110 must be removed from the body and the tip electrode 111 cleaned.

Turning now to fig. 2, a diagram of a system 200 in which one or more features of the disclosed subject matter may be implemented is illustrated, in accordance with one or more exemplary embodiments. With respect to a patient 202 (e.g., the example of patient 125 of fig. 1), system 200 includes an apparatus 204, a local computing device 206, a remote computing system 208, a first network 210, and a second network 211. Additionally, the device 204 may include a biometric sensor 221 (e.g., the example of the catheter 110 of fig. 1), a processor 222, a User Input (UI) sensor 223, a memory 224, and a transceiver 225. Note that the detection engine 101 of fig. 1 is reused in fig. 2 for ease of explanation and brevity.

According to one embodiment, the device 204 may be an example of the system 100 of fig. 1, where the device 204 may include both components internal to the patient and components external to the patient. According to another embodiment, device 204 may be a device external to patient 202 that includes an attachable patch (e.g., attached to the patient's skin). According to another embodiment, the device 204 may be inside the body of the patient 202 (e.g., implanted subcutaneously), wherein the device 204 may be inserted into the patient 202 via any suitable means, including oral injection, surgical insertion via a vein or artery, endoscopic or laparoscopic procedures. According to one embodiment, although a single device 204 is shown in fig. 2, an exemplary system may include multiple devices.

Accordingly, the apparatus 204, the local computing device 206, and/or the remote computing system 208 may be programmed to execute computer instructions with respect to the detection engine 101. For example, memory 223 stores these instructions for execution by processor 222 such that device 204 can receive and process biometric data via biometric sensor 201. As such, the processor 222 and the memory 223 represent the processors and memory of the local computing device 206 and/or the remote computing system 208.

The apparatus 204, the local computing device 206, and/or the remote computing system 208 may be any combination of software and/or hardware that individually or collectively store, execute, and implement the detection engine 101 and its functions. Additionally, the apparatus 204, the local computing device 206, and/or the remote computing system 208 may be an electronic computer framework including and/or employing any number and combination of computing devices and networks utilizing various communication technologies, as described herein. The apparatus 204, local computing device 206, and/or remote computing system 208 may be readily scalable, extensible, and modular, with the ability to change to different services or reconfigure some features independently of other features.

The networks 210 and 211 may be wired networks, wireless networks, or include one or more wired and wireless networks. According to one embodiment, network 210 is an example of a short-range network (e.g., a Local Area Network (LAN) or a Personal Area Network (PAN)). Information may be sent between the apparatus 204 and the local computing device 206 via the network 210 using any of a variety of short-range wireless communication protocols, such as bluetooth, Wi-Fi, Zigbee, Z-Wave, Near Field Communication (NFC), ultra-band, Zigbee, or Infrared (IR). Additionally, network 211 is an example of one or more of the following: an intranet, a Local Area Network (LAN), a Wide Area Network (WAN), a Metropolitan Area Network (MAN), a direct connection or series of connections, a cellular telephone network, or any other network or medium capable of facilitating communication between the local computing device 206 and the remote computing system 208. Information may be transmitted via network 211 using any of a variety of long-range wireless communication protocols (e.g., TCP/IP, HTTP, 3G, 4G/LTE, or 5G/new radio). It is noted that for either of networks 210 and 211, the wired connection may be implemented using Ethernet, Universal Serial Bus (USB), RJ-11, or any other wired and wireless connection may be implemented using Wi-Fi, WiMAX, and Bluetooth, infrared, cellular networks, satellite, or any other wireless connection method.

In operation, the device 204 may continuously or periodically obtain, monitor, store, process, and transmit biometric data associated with the patient 202 via the network 210. Additionally, the apparatus 204, the local computing device 206, and/or the remote computing system 208 communicate over the networks 210 and 211 (e.g., the local computing device 206 may be configured as a gateway between the apparatus 204 and the remote computing system 208). For example, the apparatus 204 may be an example of the system 100 of fig. 1 configured to communicate with the local computing device 206 via the network 210. The local computing device 206 may be an exampleSuch as a fixed/standalone device, a base station, a desktop/laptop computer, a smart phone, a smart watch, a tablet, or other device configured to communicate with other devices via networks 211 and 210. Public cloud computing providers implemented as physical servers on or connected to network 211 or network 211 (e.g., Amazon Web Services)) The remote computing system 208 of the virtual server in (a) may be configured to communicate with the local computing device 206 via the network 211. Thus, biometric data associated with the patient 202 may be communicated throughout the system 200.

The elements of the apparatus 204 will now be described. The biometric sensor 221 may include, for example, one or more transducers configured to convert one or more environmental conditions into electrical signals such that different types of biometric data are observed/obtained/acquired. For example, the biometric sensor 221 may include one or more of the following: electrodes (e.g., electrode 111 of fig. 1), temperature sensors (e.g., thermocouples), blood pressure sensors, blood glucose sensors, blood oxygen sensors, pH sensors, accelerometers, and microphones.

In executing the detection engine 101, the processor 222 may be configured to receive, process, and manage biometric data acquired by the biometric sensor 221, and to transfer the biometric data to the memory 224 via the transceiver 225 for storage and/or across the network 210. Biometric data from one or more other devices 204 may also be received by the processor 222 via the transceiver 225. As described in more detail below, the processor 222 may be configured to selectively respond to different tap patterns (e.g., single or double tap) received from the UI sensor 223 such that different tasks (e.g., acquisition, storage, or transmission of data) of the patch may be activated based on the detected patterns. In some implementations, the processor 222 may generate audible feedback with respect to detecting the gesture.

The UI sensor 223 includes, for example, a piezoelectric sensor or a capacitive sensor configured to receive user input such as a tap or touch. For example, in response to patient 202 tapping or touching a surface of device 204, UI sensor 223 may be controlled to achieve a capacitive coupling. Gesture recognition may be accomplished via any of a variety of capacitance types, such as resistive-capacitive, surface-capacitive, projected-capacitive, surface acoustic wave, piezoelectric, and infrared touch. The capacitive sensor may be disposed at a small area or over the length of the surface such that a tap or touch of the surface activates the monitoring device.

The memory 224 is any non-transitory tangible medium, such as magnetic memory, optical memory, or electronic memory (e.g., any suitable volatile memory and/or non-volatile memory, such as random access memory or a hard drive). Memory 224 stores computer instructions for execution by processor 222.

The transceiver 225 may include a separate transmitter and a separate receiver. Alternatively, the transceiver 225 may include a transmitter and a receiver integrated into a single device.

In operation, the device 204 utilizes the detection engine 101 to observe/obtain biometric data of the patient 202 via the biometric sensor 221, store the biometric data in memory, and share the biometric data across the system 200 via the transceiver 225. The detection engine 101 may then utilize models, algorithms (e.g., deep learning optimization), neural networks, machine learning, and/or artificial intelligence to generate and provide a mapping to the physician to reduce the processing load of the system 100 and transform the operation of the system 100 into a more accurate mapping machine.

Turning now to fig. 3, a method 300 is shown in accordance with one or more embodiments. In general, the method 300 demonstrates one or more operations of the detection engine 101 that enable depth learning optimization for detecting a maintenance focus of an aFib to be ablated to treat a persistent aFib subject and classify velocity vector field images and raw data into maintenance focuses.

The method 300 begins at block 307, where the detection engine 101 detects one or more segments of LAT (e.g., relative to a first activation time). In this regard, the input to the detection engine 101 includes biometric data in the form of ECG data signals. From the ECG data signals, one or more of the LATs are determined over at least one time interval (e.g., segment). In particular, the detection engine 101 determines a point in time (e.g., relative to a first activation time) of threshold activity corresponding to local activation that is calculated based on normalizing the initial starting point.

At block 315, the detection engine 101 computes a field, such as by modeling the vector velocity field. For example, a vector velocity field of the instantaneous velocity of the ECG data signals is measured and quantified as they pass through the LAT (e.g., by calculating the direction of the electric wave at each x, y point and providing a velocity vector field using the derivative of the polynomial surface). According to one or more embodiments, the catheter 110 may be located on a surface of the atrial (x, y) plane, and the detection engine 101 may use a scatter plot to describe the LAT (e.g., relative to the first activation time). The detection engine 101 may estimate the coefficients of the scatter plot and determine their derivatives to provide a velocity vector field.

At block 321, the detection engine 101 detects and classifies the maintenance foci. In this regard, the detection engine 101 utilizes the velocity vector field of block 315 as an input to a machine learning and/or artificial intelligence algorithm (e.g., deep convolutional neural network) to detect the location of "gold standard" maintenance foci. One or more advantages, technical effects, and/or benefits of block 321 include a big data effort that results in an understanding of a particular case outcome, including whether an ablation outcome was successful (e.g., whether and to what extent ablation therapy has one or more positive and negative outcomes). Thus, the detection engine 101 provides automatic understanding from a set of ECG signals that can be displayed via the GUI. The detection engine 101 performing the method 300 may provide a retrospective analysis that surveys past cases and determines where ablation occurred, as well as a prospective analysis for determining where ablation will be performed in future cases.

According to one or more embodiments, the detection engine 101 utilizes a machine learning algorithm, such as a neural network described herein, to determine cues in the ECG data signal regarding outcome (e.g., which portion of the data indicates when and whether the procedure has a positive outcome). The cues may also include, but are not limited to, utilizing inputs such as system status, parameters of the ablation, ablation location, ablation duration, applied force, power, and temperature. Once the tachycardia has changed due to ablation and is sustained, including, for example, extension of the tachycardia and then aborts, the machine learning algorithm of the detection engine 101 can automatically flag the event and/or location that caused the termination. The machine learning algorithm of the detection engine 101 may also mark the locations and events provided by the physician indicative of the resolved ablations in the termination predicted/expected by the machine learning algorithm. Thus, the detection engine 101 makes the user aware of the clinical outcome of the electrophysiological protocol. In addition, the operation of the detection engine 101 may be applied to other features of interest, such as HIS bundles (e.g., including special local signals) and diaphragm capture (e.g., including data segment stimulation during an AI session) and an understanding of the appearance of successful termination.

In connection with block 321 of method 300, FIG. 4 shows a graphical depiction of an artificial intelligence system 400 in accordance with one or more embodiments. The artificial intelligence system 400 includes data 410 (e.g., biometric data), a machine 420, a model 430, results 440, and (underlying) hardware 450. To facilitate understanding where appropriate, the description of fig. 4-5 is made with reference to fig. 1-3. For example, the machine 410, the model 430, and the hardware 450 may represent aspects of the detection engine 101 of fig. 1-2 (e.g., a machine learning and/or artificial intelligence algorithm therein), while the hardware 450 may also represent the catheter 110 of fig. 1, the console 160 of fig. 1, and/or the device 204 of fig. 2. In general, machine learning and/or artificial intelligence algorithms (e.g., as implemented by detection engine 101 of fig. 1-2) of artificial intelligence system 400 operate with respect to hardware 450 using data 410 to train machine 420, build model 430, and predict results 440.

For example, the machine 420 operates as or is associated with a controller or data collection associated with the hardware 450. Data 410 (e.g., biometric data as described herein) may be ongoing or output data associated with hardware 450. Data 410 may also include currently collected data, historical data, or other data from hardware 450; may include measurements during the surgical procedure and may be associated with the results of the surgical procedure; may include the temperature of the heart 140 of fig. 1 collected and associated with the results of the cardiac protocol; and may be associated with hardware 450. The data 410 may be divided into one or more subsets by the machine 420.

In addition, the machine 420 is trained, such as with respect to hardware 450. The training may also include analyzing and correlating the collected data 410. According to one or more embodiments, the detection engine 101 may train the machine learning algorithm with respect to determining that an acute arrhythmia terminated, an aFib terminated, or terminated for any tachycardia and/or with respect to identifying the results after blanking periods of several days and the notification may use long-term follow-up usage.

For example, with respect to the heart, the temperature and result data 410 may be trained to determine whether there is a correlation or link between the temperature and the result of the heart 140 of fig. 1 during a cardiac protocol. According to another embodiment, training the machine 420 may include self-training by the detection engine 101 of fig. 1 using one or more subsets. In this regard, the detection engine 101 of fig. 1 learns point-by-point detection case classification.

Further, model 430 is built on data 410 associated with hardware 450. Building model 430 may include physical hardware or software modeling, algorithmic modeling, etc. that attempts to represent data 410 (or a subset thereof) that has been collected and trained. In some aspects, the construction of the model 430 is part of a self-training operation performed by the machine 420. Model 430 may be configured to model the operation of hardware 450 and model data 410 collected from hardware 450 to predict results 440 implemented by hardware 450. The predicted results 440 (of the model 430 associated with the hardware 450) may utilize the trained model 430. For example and to enhance understanding of the present disclosure, with respect to the heart, if temperatures between 36.5 ℃ and 37.89 ℃ (i.e., 97.7 degrees fahrenheit and 100.2 degrees fahrenheit) during a procedure produce positive results from the cardiac procedure, the results 440 may be predicted using these temperatures in a given procedure. Thus, using the predicted results 440, the machine 420, model 430, and hardware 450 may be configured accordingly.

Thus, in order for the artificial intelligence system 400 to operate with respect to hardware 450 using data 410 to train the machine 420, build the model 430, and predict the results 440, the machine learning and/or artificial intelligence algorithms therein may include neural networks. A neural network is a network or circuit of neurons, or in a modern sense, an artificial neural network consisting of artificial neurons or nodes.

Artificial neural networks involve networks of simple processing elements (artificial neurons) that can exhibit complex global behavior determined by the connections between the processing elements and the element parameters. These connections of the network or circuit of neurons are modeled as weights. Positive weights reflect excitatory connections, while negative values indicate inhibitory connections. The inputs are modified by weights and summed using linear combinations. The activation function may control the amplitude of the output. For example, an acceptable output range is typically between 0 and 1, or the range may be between-1 and 1. In most cases, an ANN is an adaptive system that changes its structure based on external or internal information flowing through the network.

In more practical terms, neural networks are non-linear statistical data modeling or decision tools that can be used to model complex relationships between inputs and outputs or to find patterns in data. Thus, the ANN can be used for predictive modeling and adaptive control applications while training via a data set. Empirically generated self-learning can occur within a network, which can be concluded from a complex and seemingly unrelated set of information. Artificial neural network models are useful in that they can be used to infer a function from observations and can also be used to use that function. Unsupervised neural networks can also be used to learn representations of inputs that capture salient features of the input distribution, and recent deep learning algorithms can implicitly learn the distribution function of the observed data. Learning in neural networks is particularly useful in applications where the complexity of data (e.g., biometric data) or tasks (e.g., monitoring, diagnosing, and treating any number of various diseases) makes it impractical to manually design such functions.

Neural networks are used in different fields. Thus, for the artificial intelligence system 400, the machine learning and/or artificial intelligence algorithms therein can comprise neural networks that are generally partitioned according to the task to which they are applied. These partitions tend to fall into the following categories: regression analysis (e.g., function approximation), including time series prediction and modeling; classification, including pattern and sequence recognition; novelty detection and sequencing decisions; data processing, including filtering; clustering; blind signal separation and compression. For example, application areas for ANN include nonlinear system recognition and control (vehicle control, process control), game play and decision making (checkers, chat, competition), pattern recognition (radar systems, facial recognition, object recognition), sequence recognition (gesture, voice, handwritten text recognition), medical diagnosis and treatment, financial applications, data mining (or knowledge discovery in databases, "KDD"), visualization, and email spam filtering. For example, semantic features of patient biometric data emerging from a medical procedure may be created.

According to one or more embodiments, the neural network may implement a long-short term memory neural network architecture, a Convolutional Neural Network (CNN) architecture, or a Recurrent Neural Network (RNN) architecture, among others. The neural network may be configured with respect to multiple layers, multiple connections (e.g., encoder/decoder connections), regularization techniques (e.g., pressure differentials); and optimizing the features.

The long-short term memory neural network architecture includes feedback connections and can process single data points (such as images, for example) as well as entire data sequences (such as voice or video, for example). The cells of the long-short term memory neural network architecture may consist of cells, input gates, output gates, and forgetting gates, where cells remember values at arbitrary time intervals, and gates regulate the flow of information into and out of the cells.

The CNN architecture is a shared weight architecture with translational invariance features, where each neuron in one layer is connected to all neurons in the next layer. The regularization techniques of the CNN architecture can take advantage of hierarchical patterns in the data and assemble more complex patterns using smaller and simpler patterns. If the neural network implements a CNN architecture, other configurable aspects of the architecture may include the number of filters at each stage, the kernel size, and the number of kernels per layer.

Turning now to fig. 5, a block diagram of an example of a neural network 500 and a method 501 performed in the neural network 500 is shown, according to one or more embodiments. The neural network 500 operates to support the implementation of machine learning and/or artificial intelligence algorithms described herein (e.g., as implemented by the detection engine 101 of fig. 1-2). The neural network 500 may be implemented in hardware, such as the machine 420 and/or the hardware 450 of fig. 4. As indicated herein, the description of fig. 4-5 is made with reference to fig. 1-3 in order to facilitate understanding where appropriate.

In exemplary operation, the detection engine 101 of FIG. 1 includes collecting data 410 from hardware 450. In the neural network 500, the input layer 510 is represented by a plurality of inputs (e.g., inputs 512 and 514 of FIG. 5). With respect to block 520 of method 501, input layer 510 receives inputs 512 and 514. Inputs 512 and 514 may include biometric data. For example, the collection of data 410 may be to aggregate biometric data (e.g., BS ECG data, IC ECG data, and ablation data, along with catheter electrode position data) from one or more protocol recordings of hardware 450 into a data set (as represented by data 410).

At block 525 of the method 501, the neural network 500 encodes the inputs 512 and 514 with any portion of the data 410 (e.g., the data sets and predictions generated by the artificial intelligence system 400) to generate potential representations or data encodings. The potential representation includes one or more intermediate data representations derived from the plurality of inputs. According to one or more embodiments, the potential representation is generated by an element-level activation function (e.g., an sigmoid function or a trimmed linear unit) of the detection engine 101 of fig. 1. As shown in fig. 5, inputs 512 and 514 are provided to hidden layer 530, which is depicted as including nodes 532, 534, 536, and 538. The neural network 500 performs processing via the hidden layer 530 of nodes 532, 534, 536, and 538 to exhibit complex global behavior determined by the connections between processing elements and element parameters. Thus, the transition between layers 510 and 530 may be considered an encoder stage that takes inputs 512 and 514 and transmits them to a deep neural network (within layer 530) to learn some smaller representation of the inputs (e.g., the resulting potential representation).

The deep neural network may be a CNN, a long short term memory neural network, a fully connected neural network, or a combination thereof. Inputs 512 and 514 may be intracardiac ECG, surface ECG, or intracardiac ECG and surface ECG. This encoding provides a reduction in the dimensions of the inputs 512 and 514. Dimensionality reduction is the process of reducing the number of random variables (of inputs 512 and 514) under consideration by obtaining a set of primary variables. For example, the dimension reduction may be feature extraction that converts data (e.g., inputs 512 and 514) from a high-dimensional space (e.g., more than 10 dimensions) to a low-dimensional space (e.g., 2-3 dimensions). Technical effects and benefits of reducing dimensionality include reducing time and storage space requirements of the data 410, improving visualization of the data 410, and improving parameter interpretation for machine learning. The data transformation may be linear or non-linear. The operations of receiving (block 520) and encoding (block 525) may be considered a data preparation portion of a multi-step data manipulation by the detection engine 101.

At block 545 of method 510, the neural network 500 decodes the potential representation. The decoding stage takes some form of the encoder output (e.g., the resulting potential representation) and attempts to reconstruct the inputs 512 and 514 using another deep neural network. In this regard, the nodes 532, 534, 536, and 538 are combined to produce an output 552 in the output layer 550, as shown at block 560 of the method 510. That is, the output layer 590 reconstructs the inputs 512 and 514 in a reduced dimension, but without signal interference, signal artifacts, and signal noise. Examples of output 552 include cleaned biometric data (e.g., a cleaned/denoised version of IC ECG data or the like). The technical effects and benefits of the cleaned biometric data include the ability to more accurately monitor, diagnose, and treat any number of a variety of diseases.

Returning to fig. 3, the method 300 continues at block 330, where the detection engine 101 determines/computes a code for each point in the (x, y) plane relative to one of the four (4) directions (e.g., left may be equal to red, right may be equal to green, up may be equal to blue, and down may be equal to yellow) to provide a color-coded vector field image. The color-coded vector field image may enable a focal source or a maintenance focus to be located.

At block 345, the detection engine 101 detects a lesion/rotor indication, for example, by scanning the color-coded vector field image of block 330 using a kernel (e.g., a circle of typically 1mm radius). In general, the kernel may be a designated space within the map and may exhibit desired dimensions (e.g., circles or squares) and dimensions. In some cases, the kernel may be an address of a point within the map, a computing segment of the map, a computing boundary of the map, and so forth. In cardiac tissue, a helical wave reentry occurs when an electrically propagating wavefront encounters functionally non-excitable tissue and rotates around it in a vortex-like manner. The rotor index or rotor may then be the center of rotation from which the 2-dimensional helical field wave rotates outward. In addition, the focal indication or focus may be an arrhythmia, where the electrical impulse originates and is confined within the atrium. If within the kernel and all directions are ordered (e.g., clockwise or counterclockwise), a lesion/rotor indication may be detected. Thus, the detection engine 101 distinguishes the source of the lesion and the rotor (e.g., active and passive) on top of modeling the vector velocity field.

At block 360, the detection engine 101 marks the maintenance foci. According to one or more embodiments, the maintenance foci are tissue triggers and/or initiators that ensure the continued presence of aFib. The detection engine 101 may automatically identify or annotate an aFib maintenance lesion based on the vector velocity and ablation information. More specifically, the detection engine 101 may determine one or more gold standard annotations (e.g., the most accurate annotations) for the aFib maintenance foci. Alternatively or in combination, the physician may mark suspicious maintenance foci that may be ablated during the ablation procedure.

At block 375, the detection engine 101 classifies the lesion/rotor indication as a maintenance lesion. Classifying lesion/rotor indications into maintenance foci includes classifying active or passive regions of interest (ROIs) using machine learning and/or artificial intelligence (e.g., logistic regression classifier, support vector machine, deep learning, etc.) based on the engineered features and the vector field maps. For example, a vector velocity image with a maintenance focus standard annotation may be used as an input and/or target for a neural network (e.g., RNN or CNN as described herein) to predict whether a pixel in the vector velocity image is a maintenance focus. Further, classifying one or more lesions and/or trochanter indications as maintenance foci may utilize the velocity vector field as an input to a neural network (e.g., RNN or CNN as described herein) for detecting the location of golden standard maintenance foci.

According to one or more embodiments, ROI annotation can be used by the detection engine 101 with respect to active, passive, and unknown categories. For example, an active ROI may indicate that the ROI was ablated and the aFib terminated or the Cycle Length (CL) increased due to the ablation therapy. Active ROIs include maintenance foci with "clinical value" that includes evidence that ablation treatment near the lesion/rotor results in cycle length extension or termination of atrial fibrillation. A passive ROI may indicate that there is no visible change in the aFib characteristics including ablation therapy near the focal source in the absence of any visible change in the atrial fibrillation characteristics. Unknown annotations of the ROI may indicate that there is no visible ablation treatment near the lesion/rotor. In this manner, one or more advantages, technical effects, and/or benefits of the detection engine include addressing most points of the map that are not addressed by the physician because the physician is unaware of the active or passive nature of the ROI. The detection engine 101 may also assign probabilities across active, passive, and unknown classes (e.g., a scale of 0 to 100 indicates the likelihood of a class).

Note that with respect to the operations of blocks 321, 360, and 375, the detector engine 101 may utilize the results of any operation as feedback or input to another operation, as indicated by the double arrow.

Turning now to fig. 6, a method 600 in accordance with one or more embodiments is illustrated. Generally, the method 600 demonstrates one or more operations of the detection engine 101 to implement optimization to detect atrial fibrillation maintenance foci to be ablated for treatment.

At block 605, method 600 begins, where detection engine 101 receives one or more inputs, such as IC ECG data signals, from catheter 110. At block 610, the detection engine 101 detects a segment of the LAT. Fig. 7 illustrates a graph 700 in accordance with one or more embodiments. As shown in fig. 7, a segment of the LAT is detected relative to the time of activation relative to the first activation time (shown as circle 710).

At block 625, the detection engine 101 determines/calculates/models the vector velocity field. In this regard, the detection engine101 assume that catheter 110 is located on the surface of the atrial (x, y) plane and a scatter plot is used to describe the activation time (e.g., relative to the first activation time described as a circle in fig. 7). Fig. 8 shows a graph 800 of a surface (x, y) in accordance with one or more embodiments. Graph 800 provides a graph of Z milliseconds (msec) including surface (x, y) and activation time in the section. Given the graph 800, the detection engine 101 may estimate the coefficients of the surface (x, y) that best fits its points. The polynomial surface T (x, y) can use gradient descent to estimate N and a relative to a cost function (as seen in equation 1)_i,jAt position x_s,y_sMeasured L local activation time and (x)_s,y_s) Estimated surface in plane T (x)_s,y_s) The mean square error between is minimized by a regularization term (p is typically equal to 0.1) that takes into account the number of parameters estimated in the model. More specifically, the polynomial surface may be defined by equation 2.

From T (x, y) to the vector field, a model can be used to calculate the direction of the electric wave at each point in (x, y) defined by equation 3.

T_xDefined by equation 4.

Fig. 9 illustrates a graph 900 of a velocity vector field of the surface (x, y) of fig. 8 in accordance with one or more embodiments. That is, the derivative of the polynomial surface of FIG. 8 provides the velocity vector field shown in FIG. 9.

At block 630, each point in the (x, y) plane is encoded into one of four (4) directions to provide a color-coded vector field image so that a focal source or a maintenance focus can be located.

At block 645, a lesion/rotor may be detected by the detection engine 101. For example, the detection engine 101 may use a kernel (typically a circle with a radius of 1 mm) to scan the color-coded vector field image obtained in block 630. If within the inner core and all 4 directions appear in sequence (clockwise or counterclockwise), the trochanter/focal point is detected.

At block 660, the maintenance foci may be marked by the detection engine 101. At block 675, the lesion/rotor indication may be classified as a maintenance lesion by the detection engine 101.

The flowchart and block diagrams in the figures illustrate the architecture, functionality, and operation of possible implementations of systems, methods and computer program products according to various embodiments of the present invention. In this regard, each block in the flowchart or block diagrams may represent a module, segment, or portion of instructions, which comprises one or more executable instructions for implementing the specified logical function(s). In some alternative implementations, the functions noted in the block may occur out of the order noted in the figures. For example, two blocks shown in succession may, in fact, be executed substantially concurrently, or the blocks may sometimes be executed in the reverse order, depending upon the functionality involved. It will also be noted that each block of the block diagrams and/or flowchart illustration, and combinations of blocks in the block diagrams and/or flowchart illustration, can be implemented by special purpose hardware-based systems that perform the specified functions or acts, or combinations of special purpose hardware and computer instructions.

Although features and elements are described above with particularity, those of ordinary skill in the art will recognize that each feature or element can be used alone or in any combination with the other features and elements. Furthermore, the methods described herein may be implemented in a computer program, software, or firmware incorporated in a computer-readable medium for execution by a computer or processor. As used herein, a computer-readable medium should not be understood as a transitory signal per se, such as a radio wave or other freely propagating electromagnetic wave, an electromagnetic wave propagating through a waveguide or other transmission medium (e.g., a light pulse traveling through a fiber optic cable), or an electrical signal transmitted through a wire.

Examples of computer readable media include electronic signals (transmitted over a wired or wireless connection) and computer readable storage media. Examples of computer readable storage media include, but are not limited to, registers, cache memory, semiconductor memory devices, magnetic media such as internal hard disks and removable magnetic disks, magneto-optical media, optical media such as Compact Disks (CDs) and Digital Versatile Disks (DVDs), Random Access Memories (RAMs), Read Only Memories (ROMs), erasable programmable read only memories (EPROMs or flash memories), Static Random Access Memories (SRAMs), and memory sticks. A processor associated with software may be used to implement a radio frequency transceiver for use in a terminal, base station, or any host computer.

It is to be understood that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting. As used herein, the singular forms "a", "an" and "the" include plural references unless the context clearly dictates otherwise. It will be further understood that the terms "comprises" and/or "comprising," when used in this specification, specify the presence of stated features, integers, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, element components, and/or groups thereof.

The description of the various embodiments herein is presented for purposes of illustration, but is not intended to be exhaustive or limited to the disclosed embodiments. Many modifications and variations will be apparent to those of ordinary skill in the art without departing from the scope and spirit of the described embodiments. The terminology used herein is chosen to best explain the principles of the embodiments, the practical application or technical improvements over commercially available technology, or to enable others of ordinary skill in the art to understand the embodiments disclosed herein.