Patent Application
20250204976
The present disclosure relates generally to detection of respiration effects, and specifically to detecting the times of ends of expirium.
Techniques to compensate for respiratory effects were previously reported in patent literature. For example, U.S. Pat. No. 10,524,692 describes a method including positioning body-electrodes in galvanic contact with a body of a patient and locating a probe in the body of the patient. The method further includes tracking positions of the probe during respiration of the patient and determining indications related to impedances between the body-electrodes during the respiration. The method also includes calculating a function relating the positions of the probe to the indications, and applying the function to identify end-expirium points of the respiration based on subsequent indications related to the impedances.
The present disclosure will be more fully understood from the following detailed description of the examples thereof, taken together with the drawings, in which:
A wide range of medical procedures involve the use of invasive probes, such as cardiac catheters to diagnose and/or treat a patient. The quality of the medical application may depend on detection of the end of the exhalation part of the respiratory cycle (referred to herein as “end-of-expirium”). Timing a medical procedure to occur at the end-of-expirium is desirable, due to, for example, relaxation in internal motion. For example, applying cardiac ablation during end-of-expirium may be safer and more accurate.
During the breathing cycle, a body's measured electrical impedance tends to be affected by the lungs alternately being filled with, and then emptied of, air, since air is an insulator. Examples of the present disclosure that are described herein provide a technique to follow a total body impedance indication calculated from conductivities measured using patch electrodes attached to the skin of the patient's trunk (e.g., at the back and thorax regions). The disclosed total body impedance indication is found to be well correlated to lungs emptied of air at the end-of-expirium. In some examples, the disclosed technique utilizes several patch electrodes attached to the skin of a patient to measure a combined impedance matrix ρ or a combined conductivity matrix σ that, respectively, describe the combined impedance or conductance of the patch electrodes and a patient body's respective impedance or conductance.
The patch electrodes used can be these of an electrical tracking system already in place (e.g., to track the position of a catheter inside the heart). In such a case, each patch acts as a transmitter of an AC signal in a unique frequency, while the other patches act as receivers. In this way, the system can receive multiple AC signals, and based on these signals, a processor can calculate the combined impedance or conductivity matrix, ρ or σ.
An example of a method and technique to obtain a combined conductivity matrix σ is described in U.S. Pat. Nos. 8,456,182 and 10,524,692, both assigned to the assignee of the current application. The inventors noted that a parameter best describing the subject's torso impedance is the sum over all patches of patch-to-patch conductivities. This sum can be obtained by calculating the diagonal sum (e.g., matrix trace) of conductivity matrix σ.
To this end, in some examples, a processor uses the value of the reciprocal of the trace of matrix σ, R(t)=1/Tr(σ), where t is time. Times at which the lungs are most emptied of air (i.e., the ends-of-expirium) during respective respiration cycles are manifested as minima of the time-dependent total impedance function R(t).
The processor can output the timings of end-of-expirium to a user as an algorithm (e.g., by tagging the minima, and outputting the tags, to a cardiac ablation algorithm). Alternatively, or additionally, the processor may output the timings of end-of-expirium by displaying curve R(t) on a display device.
The disclosed end-of-expirium detection technique was found accurate and robust in the service of cardiac ablation, as well as other electrical noise-inducing phenomena during invasive and noninvasive treatments that require end-of-expirium detection. In general, the disclosed technique may be applied as described below, with a standalone processor or with a processor of any medical system that requires the use of the technique (e.g., a medical imaging system that requires respiratory gating).
System 10 includes multiple catheters which are percutaneously inserted by physician 24 through the patient's vascular system into a chamber or vascular structure of a heart 12 (seen in inset 45). Typically, a delivery sheath catheter is inserted into a cardiac chamber, such as the left or right atrium near a desired location in heart 12. Thereafter, a plurality of catheters is inserted into the delivery sheath catheter in order to arrive at the desired location. The plurality of catheters may include a catheter dedicated for pacing, a catheter for sensing intracardiac electrogram signals, a catheter dedicated for ablating and/or a catheter dedicated for both EA mapping and ablating. An example catheter 14, illustrated herein, is configured for sensing bipolar electrograms. Physician 24 brings a distal tip 28 (also called hereinafter distal end assembly 28) of catheter 14 into contact with the heart wall for sensing a target site in heart 12. For ablation, physician 24 similarly brings a distal end of an ablation catheter to a target site.
As seen in inset 65, catheter 14 is an exemplary catheter that includes a basket distal end 28, including one, and preferably multiple, electrodes 26 optionally distributed over a plurality of splines 22 at distal tip 28 and configured to sense IEGM signals. Catheter 14 may additionally include a position sensor 29 embedded in or near distal tip 28 on a shaft 46 of catheter 14, used to track the position and orientation of distal tip 28. Optionally, and preferably, position sensor 29 is a magnetic-based position sensor including three magnetic coils for sensing three-dimensional (3D) position and orientation. As seen, distal tip 28 further includes an expansion/collapse rod 42 of expandable assembly 28 that is mechanically connected to basket assembly 28 at a distal edge 41 of assembly 28.
Magnetic based position sensor 29 may be operated together with a location pad 25 that includes a plurality of magnetic coils 32 configured to generate magnetic fields in a predefined working volume. Real-time position of distal tip 28 of catheter 14 may be tracked based on magnetic fields generated with location pad 25 and sensed by magnetic based position sensor 29. Details of the magnetic based position sensing technology are described in U.S. Pat. Nos. 5,391,199; 5,443,489; 5,558,091; 6,172,499; 6,239,724; 6,332,089; 6,484,118; 6,618,612; 6,690,963; 6,788,967; 6,892,091.
System 10 includes one or more electrode patches 38 positioned for skin contact on patient 23 to establish a location reference for location pad 25 as well as impedance-based tracking of electrodes 26. For impedance-based tracking, electrical current is directed toward electrodes 26 and sensed at electrode skin patches 38 so that the location of each electrode can be triangulated via electrode patches 38. Details of the impedance-based location tracking technology are described in U.S. Pat. Nos. 7,536,218; 7,756,576; 7,848,787; 7,869,865; 8,456,182; and 10,524,692.
Electrode patches 38 can be used, in a stand-alone fashion with a processor running the disclosed algorithm, to electrically detect an end-of-expirium, as described in
A recorder 11 displays, on display device 27, cardiac signals 21 (e.g., electrograms acquired at respectively tracked cardiac tissue positions) acquired with body surface ECG electrodes 18 and intracardiac electrograms acquired with electrodes 26 of catheter 14. Recorder 11 may include pacing capability to pace the heart rhythm, and/or may be electrically connected to a standalone pacer.
Workstation 55 includes memory 57, a processor 56 unit with memory or storage with appropriate operating software loaded therein, and user interface capability. Workstation 55 may provide multiple functions, optionally including (i) modeling endocardial anatomy in three-dimensions (3D) and rendering the model or EA map 20 for display on display device 27, (ii) displaying activation sequences (or other data) compiled from recorded cardiac signals 21 in representative visual indicia or imagery superimposed on the rendered EA map 20 on display device 27, (iii) displaying real-time location and orientation of multiple catheters within the heart chamber, and (iv) displaying sites of interest on display device 27, such as places where ablation energy has been applied. One commercial product embodying elements of system 10 is available as the CARTO™ 3 System, available from Biosense Webster, Inc., 31A Technology Drive, Irvine, CA 92618.
System 10 may include an ablation energy generator 50 that is adapted to conduct ablative energy to one or more electrodes at a distal tip of a catheter configured for ablation. Energy produced by ablation energy generator 50 may include, but is not limited to, radiofrequency (RF) energy or pulsed-field ablation (PFA) energy, including monopolar or bipolar high-voltage DC pulses, to be used to effect irreversible electroporation (IRE), or combinations thereof.
Patient interface unit (PIU) 30 is an interface configured to establish electrical communication between catheters, electrophysiological equipment, power supply and a workstation 55 to control system 10 operation and to receive EA signals from the catheter. Electrophysiological equipment of system 10 may include, for example, multiple catheters, location pad 25, body surface ECG electrodes 18, electrode patches 38, ablation energy generator 50, and recorder 11. Optionally, and preferably, PIU 30 additionally includes processing capability for implementing real-time computations of catheter locations and for performing ECG calculations.
In some examples, processor 56 typically comprises a general-purpose computer, which is programmed in software to carry out the functions described herein. The software may be downloaded to the computer in electronic form, over a network, for example, or it may, alternatively or additionally, be provided and/or stored on non-transitory tangible media, such as magnetic, optical, or electronic memory.
This configuration of system 10 is shown by way of example, in order to illustrate certain problems that are addressed by examples of the present disclosure and to demonstrate the application of these examples in enhancing the performance of such a system. Examples of the present disclosure, however, are by no means limited to this specific sort of example system, and the principles described herein may similarly be applied to other types of medical systems. For example, other multi-electrode catheter types may be used, such as the multi-arm OCTARAY™ catheter or a flat catheter.
While the disclosed technique is described using
AC signal sources 208 apply an AC signal between each respective patch electrode 206 and a common ground 214. AC signal meters 210 measure resulting AC signals between each of the patch electrodes 206 and the common ground 214. AC signal generator sources 208 each transmit at a unique frequency fj. The body's changing impedance, due to breathing, affects the measured AC signal that is received (209) at the rest of patches 206.
Using the AC signals measured by meters 210, processor 56 of
One possible reason to consider using the disclosed method (e.g., graph 333) in cardiac ablation: is its simplicity compared with the method of U.S. Pat. No. 10,524,692. Another possible reason to consider using the disclosed method in cardiac ablation is that graph 333 shows that the disclosed method is less affected by the high voltage or current signals that cardiac ablation applies during time windows (seen as “ones” in curve 335).
Next, at a total conductivity calculation step 404, a processor uses the measured conductivities to calculate a total conductivity value, such as Tr(σ). Next, in a total impedance calculation step 406, the processor derives a measure of the total impedance, such as 1/Tr(σ). Steps 404 and 406 are brought, in some excess detail, for clarity of the exemplified method, though these steps may be reduced into a single step in other examples.
In minima relating step 408, the processor relates the minima of 1/Tr(σ) to timings of end-of-expirium, for example, by tagging the minima for use in cardiac ablation.
Finally, at an outputting step 410, the processor outputs the timings of end-of-expirium as an algorithm (e.g., a cardiac ablation algorithm). The processor outputs the timings of end-of-expirium by displaying curve 333 on a display device 27.
The example flow chart shown in
A method includes measuring impedances of a body using a plurality of electrodes (38) attached to a patient (23), as a function of time. A total impedance value is calculated from the measured impedances, as a function of time. Temporal minima of the total impedance value are related with timings of end-of-expirium of the patient. The timings of end-of-expirium are outputted to a user.
The method according to example 1, wherein the plurality of electrodes (38) comprise electrodes of an electrical position-tracking system (10).
The method according to any of examples 1 and 2, wherein calculating the total impedance value comprises calculating a reciprocal of a trace of a conductivity matrix σ.
The method according to any of examples 1 through 3, and comprising applying a medical procedure to the patient (23) at time-windows around the timings of end-of-expirium.
The method according to any of examples 1 through 4, wherein the medical procedure comprises cardiac ablation.
The method according to any of examples 1 through 5, wherein outputting the timings comprises outputting the timings to a cardiac ablation algorithm.
The method according to any of examples 1 through 5, wherein outputting the timings comprises displaying the timings on a display device (27).
A system (10) includes circuitry (200) and a processor (56). The circuitry (200) is configured to measure impedances of a body using a plurality of electrodes (38, 206) attached to a patient (23), as a function of time. The processor (56) is configured to (i) calculate a total impedance value from the measured impedances, as a function of time, (ii) relate temporal minima of the total impedance value with timings of end-of-expirium of the patient, and (iii) output the timings of end-of-expirium to a user.
Although the examples described herein mainly address cardiac diagnostic applications, the methods and systems described herein can also be used in other medical applications.
It will be appreciated that the examples described above are cited by way of example, and that the present disclosure is not limited to what has been particularly shown and described hereinabove. Rather, the scope of the present disclosure includes both combinations and sub-combinations of the various features described hereinabove, as well as variations and modifications thereof which would occur to persons skilled in the art upon reading the foregoing description and which are not disclosed in the prior art.
