Source: https://patents.google.com/patent/JP2016512460A/en
Timestamp: 2019-11-14 02:43:24
Document Index: 218997611

Matched Legal Cases: ['art 150', 'art 150', 'art 150', 'art 180', 'art 180', 'art 180']

JP2016512460A - Method and apparatus for realizing a dual reference for arrhythmia detection - Google Patents
Method and apparatus for realizing a dual reference for arrhythmia detection Download PDF
JP2016512460A
JP2016512460A JP2016501042A JP2016501042A JP2016512460A JP 2016512460 A JP2016512460 A JP 2016512460A JP 2016501042 A JP2016501042 A JP 2016501042A JP 2016501042 A JP2016501042 A JP 2016501042A JP 2016512460 A JP2016512460 A JP 2016512460A
JP2016501042A
2013-03-11 Priority to US201361776326P priority Critical
2013-03-11 Priority to US61/776,326 priority
2014-03-10 Application filed by キャメロン ヘルス、 インコーポレイテッド, キャメロン ヘルス、 インコーポレイテッド filed Critical キャメロン ヘルス、 インコーポレイテッド
2014-03-10 Priority to PCT/US2014/022713 priority patent/WO2014164530A1/en
2016-04-28 Publication of JP2016512460A publication Critical patent/JP2016512460A/en
A method and apparatus for providing a plurality of criteria for use in arrhythmia identification. One of a more conservative set or a more aggressive set of arrhythmia identification parameters may be selected based on inputs including defined rules or parameters. For example, one or the other of the selectable set of arrhythmia identification parameters may also be adaptable or changeable during use of the system, eg, in response to an identified non-persistent episode. The more conservative set of arrhythmia identification parameters can be changed to be even more conservative. Such a change in the arrhythmia discrimination criteria, if indicated, allows a reduction in time to treatment, while in other situations it allows more careful judgment.
The present invention relates to a method and apparatus for implementing a dual reference for arrhythmia detection.
Implantable cardiac stimulators, including implantable defibrillators, face conflicting design goals. A balance must be struck between careful treatment decisions that avoid inappropriate or unnecessary treatment and aggressive treatment decisions that prevent loss of consciousness and maximize the chances of successful recovery. .
Further alternatives are needed to address these conflicting objectives.
The present invention includes an implantable device that implements a dual and adaptable arrhythmia detection criterion and a method of operation in the implantable device. The inventors have discovered a combination of adaptive and fixed criteria for arrhythmia detection, referred to herein as “dual” criteria. In one example, by observing the characteristics of the sensed cardiac signal, one or the other of the first and second criteria is selected and applied to the cardiac signal for performing arrhythmia analysis. The first criterion is applied when a highly malignant arrhythmia index is identified, and the second criterion is applied when a low malignant arrhythmia index is identified. In one example, the criteria changed may include persistence data or quantity data, and clearly for lower grade arrhythmias, a longer duration of evidence or a larger quantity of evidence is required. The present invention may be implemented in apparatus and methods and as a non-transitory medium that includes software instructions.
Further embodiments may include the application of gradients of arrhythmia discrimination criteria in response to potential input gradients that extend beyond the “double” criterion to multi-layer criteria. In some examples, the electrical heart signal is evaluated to determine which criteria to apply, while in other examples, blood component concentrations, blood pressure, accelerometer inputs, or from other implantable devices Other inputs such as communications are used.
This summary provides an overview of the subject matter of the present patent application. This summary is not intended to provide an exclusive or exhaustive description of the invention. A detailed description is included to provide more detailed information about the present patent application.
In the drawings, which are not necessarily drawn to scale, the same numerals may describe similar components in different fields of view. Identical numbers with different letter suffixes may represent different examples of similar components. The drawings generally illustrate, by way of example and not by way of limitation, various embodiments that are discussed in this document.
The figure which shows the method of the analysis in an implantable heart apparatus in a block format. The figure which shows management of the arrhythmia detection reference | standard function which can be applied in a block format. The figure which shows the selection between the 1st reference | standard of an arrhythmia identification, and a 2nd reference | standard in a block / flow format. The figure which shows the implantable cardiac stimulation apparatus and transvenous implantable cardiac stimulation apparatus of only a subcutaneous. The figure which shows the implantable cardiac stimulation apparatus and transvenous implantable cardiac stimulation apparatus of only a subcutaneous. Diagram showing analysis method in block format FIG. 4 illustrates another exemplary embodiment in block form. The figure which shows another analysis method.
The following detailed description should be read with reference to the drawings. The drawings are not necessarily to scale, but represent exemplary embodiments and are not intended to limit the scope of the invention. Unless explicitly stated or explicitly stated, the examples of the method in this application should not be read to require any particular order of steps.
In the present application, a signal is sensed by the implantable heart device, an event in the sensed signal is detected, and the heart rhythm is classified by use of the detected event (hereinafter referred to as “detection event”). A detection event may also be referred to as detection. The classification of heart rhythm can be referred to as rhythm analysis. The classification of cardiac rhythm can include the identification of malignant conditions such as ventricular fibrillation or certain tachyarrhythmias.
Implantable treatment systems typically rely on rhythm classification to make treatment / stimulation decisions, while monitoring systems typically use rhythm classification to record data when applicable. Make a decision. Any of these systems, when so configured and enabled, can generate an announcement (electronic sound or obvious vibration) signal or a communication (telemetry) signal, depending on the rhythm classification. . The present invention may be used in an implantable monitoring or treatment system.
When detecting an event, the implantable heart device may compare the sensed signal to a detection threshold. If / when the sensed signal exceeds the detection threshold, a new detection event is declared. The detection threshold may be fixed or may change over time (or depending on other variables such as observed signal frequency) depending on the system configuration. In some systems, the detection threshold has a shape defined by a detection profile that can be newly applied after each detection event.
The cardiac cycle is typically in accordance with well-known conventions several parts (often “waves”) labeled by letters containing P, Q, R, S and T, respectively corresponding to a particular physiological event. Called). Each cardiac cycle usually has all of these parts, but not all may be visible in the representation of a given cardiac signal. Certain components may not be visible due to factors such as high rates, selection of sensing vectors, anatomical abnormalities, or active arrhythmia. The combination of Q, R and S “waves” may be referred to as a QRS complex.
The concepts of sensing, detection and rhythm classification are integrated into the method shown in FIG. 1 by way of illustration. The implantable device can be configured to sense the signal until a detection event is detected, as previously described. In the method of FIG. 1, the new detection is identified at reference numeral 10. US Pat. No. 8,565,878, whose disclosure is incorporated herein by reference, entitled “ACCURATE CARDIC EVENT DETECTION IN AN IMPLANTABLE CARDIAC STIMULUS DEVICE”, is a detection profile and method / apparatus for detecting events. Although some examples are provided, other techniques may be used.
The exemplary system then moves on to removing noise and overdetection as shown at reference numeral 12. Various methods can be used to identify and remove those detection events caused by noise and overdetection. Some examples of noise discrimination are "ADA
U.S. Patent Application Publication No. 2011-0098775 entitled "PTIVE WAVEFORM APPRIAL IN IN IMPLANTABLE CARDIAC SYSTEM". The disclosure of said document is incorporated herein by reference. Some examples of overdetection identification are US Pat. No. 8,265,737 entitled “METHODS AND DEVICES FOR IDENTIFYING OVERDETECTION OF CARDIAC SIGNALS” and “METHODS AND
U.S. Pat. Nos. 8,160,686 and 8,160,687 entitled "DEVICE FOR FOR ACCURRATELY CLASSIFYING CARDIAC ACTIVITY", the disclosures of which are incorporated herein by reference. Alternatively, other methods of identifying and removing noise and overdetection may be used. It is typical, but not essential, to design the detection structure such that each cardiac cycle is often counted once by finding the occurrence of an R wave or QRS complex. In some cases, a P wave may be observed instead, as may be the case with a device having an atrial lead.
One approach to block 12 is to identify noise detection, for example, by observing whether an inflection point or threshold for inflection is exceeded. In one example, if at least a threshold number of inflections occur during a period associated with a detection event, the detection event is deemed suspicious due to noise and the suspicious event is discarded. In another example, turning points or inflections that occur between detection events may be counted directly or using a metric per unit time and compared to a threshold value.
Another approach to block 12 is to identify overdetection by applying criteria to observe the alternating shape pattern of detection events. In that case, an alternating shape may indicate overdetection if at least some of the detections match each other or match the template, but others do not match. Another approach to block 12 is to identify overdetection by observing whether alternating spacing patterns appear between detection events. In that case, the alternating spacing pattern may indicate over-detection if the spacing is clustered over time, such as having pairs of long and short intervals. Another approach to block 12 identifies overdetection by observing whether closely paired detections have a shape that suggests that the two detections are both related to the same QRS complex or beat. That is.
These exemplary methods for noise and over-detection identification may be used in various combinations, and the examples given are merely illustrative. Other techniques may be used.
Once identified noise and overdetection removal can take many forms, including those described in US Pat. No. 8,160,686. Said patent document is incorporated herein by reference. For example, a detection identified as overdetection may be ignored, and the interval between the identified overdetection and two temporally adjacent detections is a single interval for purposes of determining heart rate. Allows to be combined. In contrast, a detection that has been identified as suspicious but without a strong conclusion of overdetection can be discarded along with the interval between the suspicious event and two temporally adjacent detections.
As indicated at reference numeral 14, the method also includes obtaining rate and shape data. The elements of blocks 12 and 14 may overlap or may be performed in a different order in various implementations. The rate can be obtained by calculating the average of the intervals between several detections. In that case, noise and overdetection may be excluded before calculating the rate. The shape data may include information related to average amplitude, peak amplitude, width, turning point, frequency components and other features, and amplitude for each sample. For example, shape data may be generated and / or analyzed by using correlation waveform analysis, principal component analysis, wavelet decomposition or Fourier transform or other mathematical transforms. In some examples, shape data is generated for individual detections. In some examples, shape data is generated for a predetermined period spanning several detections, eg, calculating the data over a 3 second time window (or other duration).
There are many ways to evaluate shape data to distinguish between malignant and non-malignant heart rhythms. Some examples are described in US Pat. No. 7,330,757, entitled “METHOD FOR DISCRIMINATING BETWEEN VENTRICULAR AND SUPREVENTURER ARRHYTHMIAS”. The disclosure of said document is incorporated herein by reference.
In the example of FIG. 1, the rate and shape data from block 14 is provided to rhythm analysis 16, optionally with information about the noise and overdetection evaluation results at reference numeral 12. Rhythm analysis 16 includes, in this application, reviewing multiple detections to classify the condition of the patient's heart.
For example, in one instance, the rhythm analysis considers an analysis of a set of Y detections and determines how many Xs in the Y detections are indicative of an ongoing malignant arrhythmia, Using a / Y counter. The calculation of X may include an evaluation of the rate calculated for at least some of the Y detections, shape data for at least some of the Y detections, and / or combinations thereof. Some examples in the art use an analysis that refers to a “number of intervals to detect” marker, sometimes abbreviated as “NID”. The NID can be viewed as a subset of X / Y counters according to the approach presented herein.
In the example, the rhythm analysis is layered. For example, in the first tier, if the rate is calculated for a given event, if it is higher than the VF threshold, the event is considered “treatable” without having to consider other factors. In the next layer, if the rate is less than the “VF threshold” and higher than the “VT threshold” when calculated for a given event, it is narrow unless it matches the static template, or As long as it does not match the dynamic template, the event is considered “treatable”. Finally, in the third layer, if the rate is less than the VT threshold when calculated for a given event, the event is not considered “treatable”. Other criteria may be applied and additional layers or analytics may be used.
US Pat. No. 6,754,528, entitled “APPARATUS AND METHOD OF OF ARRHYTHMIA DETECTION IN A SUBCUTANEOUS IMPLANTABLE IMPRONTABLE CARDIOVERTER / DEFIBRILLATOR”, is incorporated herein by reference, and is incorporated by reference. An example using an X / Y counter is shown in US Pat. No. 8,160,697. Said patent document is incorporated herein by reference. When using an X / Y counter, thresholds such as 8/12, 18/24, 30/40 or more can be used as desired for the X / Y counter. For example, if an X / Y threshold of 18/24 is used, when X reaches 18 or exceeds 18, the X / Y counter condition is met, indicating the possibility of the presence of an arrhythmia. Many implantable heart systems incorporate an X / Y counter in their analysis, but an X / Y counter is not required. FIG. 2 provides additional discussion of exemplary methods in the following.
The rhythm analysis 16 may determine that the current rhythm does not appear to be treatable in the example shown in FIG. 1, in which case the method is as follows, as indicated by the dashed line leading to block 10: The process ends at block 24 until a new detection occurs. Rhythm analysis 16 may instead determine that the current rhythm seems to be actually treatable.
If the rhythm analysis 16 concludes that there is a treatable arrhythmia, the exemplary method continues to the charge confirmation step 18. In the example, the charge confirmation 18 requires the result of a rhythm analysis that seeks to continue treatment. For example, confirmation 18 may require the results of a rhythm analysis that lasts for a set period or for a prescribed amount of successive iterations. In some examples, rhythm analysis 16 and charge confirmation 18 may be combined into a single integrated evaluation. In one instance, the charge confirmation requires N consecutive iterations of the rhythm analysis to track the variable “N” and arrive at a result that requires treatment. Some details about persistence changes are discussed below with respect to FIG.
In the example of FIG. 1, an “episode” is declared as highlighted in reference numeral 26 after successful completion of the charging confirmation 18 that determines that treatment should be performed. Episode declarations can suggest several things to those skilled in the art. In some examples, once an episode is declared, certain data, such as the amount of recorded signal data, is stored in the long-term memory of the implantable device for later retrieval by the physician. Episode declarations can also occur simultaneously with the start of preparation for treatment delivery, such as filling a capacitor to allow treatment delivery.
In some instances, the episode declaration occurs at the same time that the device enters the “review” state, which initiates enhanced analysis and results in data storage, but does not prepare for treatment initiation. For example, the episode may be declared before the charging confirmation 18 as indicated by the dashed line from the episode declaration 26 shown in FIG.
Declaration of an episode can lead to the start of providing anti-tachycardia pacing (ATP) or can occur simultaneously. Episodic declarations, for example, by alerting the patient or health care system, such as by generating an electronic sound or vibration to inform the patient of possible impending treatment delivery, or by RF or other telemetry Such as the occurrence of an electronic transmission to a monitoring or programming system, or the generation of an emergency alert for transmission to an emergency dispatch.
In the exemplary method, the next decision block is treatment confirmation 20. In this example, the treatment confirmation 20 is performed when preparation for treatment is completed or almost completed. For example, a capacitor for providing high voltage therapy may be charged or may be almost fully charged. In some examples (including ATP), the provision of ATP can be completed, but the episode does not end in response to ATP. For such an example, passing block 18 may provide ATP, but the high energy shock for defibrillation will wait until ATP is complete and treatment confirmation 20 is satisfied.
For example, treatment confirmation 20 may include confirming that the selected criteria indicative of malignant arrhythmia continues to exist. In one example, treatment confirmation 20 confirms that the detected rate of the patient's cardiac event has exceeded the treatment limit immediately prior to providing treatment. Some examples of treatment confirmation are: “ADAPTIVE CONFIRMATION OF TREATABLE”
U.S. Patent Application Publication No. 2010-0331904 entitled "ARRHYTHMIA IN IMPLANTABLE CARDIA STIMULUS DEVICES". The disclosure of said document is incorporated herein by reference. Other confirmations may be made in the treatment confirmation 20, or alternatively, the treatment confirmation 20 may be omitted.
Once the treatment preparation is complete and passes through each of the analysis blocks 16, 18, 20, treatment may be provided at block 22. Treatment delivery may be performed in any suitable manner, including transvenous electrodes, epicardial electrodes, or subcutaneous electrodes, in various combinations and energy levels. Boston Scientific's Teligen® ICD and S-ICD® systems, Medtronic's Concerto® and Virtuoso® systems, and St. Jude Medical (St. A variety of commercially available systems are known that can provide treatment, including Jude Medical's Promote® RF and Current® RF systems. Some examples of providing subcutaneous-only treatments are “ADAPTIVE SHOCK DELIVERY IN AN IMPLANTABLE CARDIAC”.
U.S. Pat. No. 8,244,349 entitled "STIMULUS DEVICE". The disclosure of said patent document is incorporated by reference.
After providing treatment, there may be a period of post-shock blanking as indicated at reference numeral 22 and various other activities may occur. In one instance, the method of US Pat. No. 8,494,630 entitled “DATA MANIPULATION FOLLOWING DELIVERY OF A CARDIAC STIMULUS IN AN IMPLANTABLE CARDIAC STIMULUS DEVICE” is intended to provide further analysis, Applied to prepare implantable devices. The disclosure of said document is incorporated herein by reference. Multiple shocks can be provided during a particular episode. In some examples, one or more analysis steps of FIG. 1 may be modified following the provision of a first treatment shock during a given episode.
The particular steps shown in FIG. 1 may be simplified or omitted in some embodiments. In the illustration, the additional element is one of blocks 16, 18, 20 to make the overall treatment decision more aggressive or less aggressive depending on the identified criteria. Used to adjust the process followed. In some embodiments, additional steps / processes beyond those shown may be performed. For example, anti-tachycardia pacing may be applied before or after charging confirmation 18 and / or episode declaration 26.
FIG. 2 shows the management of the adaptive arrhythmia detection criteria function in block form. The method begins with the identification of non-persistent episodes at block 50. Non-persistent episodes are those for which no treatment is provided after the episode declaration.
An example of a non-persistent episode is an episode caused by intermittent noise, such as intermittent / temporary skeletal noise or external noise, or by noise ending before treatment delivery. Such noise may cause the implantable device to falsely identify high rate arrhythmias. If the noise is intermittent and terminates before delivery of therapy, modern devices will generally not deliver a shock if the end of a high rate condition is identified before delivery of therapy. Another source of such episodes may be a lead disorder or an impending lead disorder that is a known source of both non-persistent episodes and pre-treatment noise-related episodes in transvenous ICD patients. As shown at reference numeral 52, these would be non-persistent episodes with noise.
For example, non-persistent episodes can also occur when a patient has non-persistent ventricular tachycardia, meaning that a short burst of high-rate detection events has occurred. Another example is an episode that starts due to a false detection (such as double detection) of a cardiac signal that later resumes accurate detection. Such an episode would be an untreated episode 54 with no noise.
In response to a non-persistent episode, the detection architecture may be configured to change the episode criteria, as indicated by reference numeral 56. Some examples include increasing the parameters used to define the arrhythmia in the X (X-out-of-Y) counter by changing X and / or Y.
One particular example of changing the episode criteria is to raise the criteria applied to the X / Y counter, as indicated by reference numeral 58. Another example of changing the episode criteria is an extension of the persistence criteria 60. An exemplary discussion of each of raising the X / Y counter standard 58 and applying the sustainability standard 60 is provided in US Pat. No. 8,160,697. Said patent document is incorporated herein by reference. Such changes must, in part, reduce the sensitivity to non-persistent episodes and can delay episode declarations to prevent certain systems from repeatedly declaring episodes. . The repeated declaration may unnecessarily run out of battery capacity and / or increase the possibility of providing inappropriate treatment. However, such changes may also delay the declaration of episodes for events that require treatment, such as persistent ventricular fibrillation.
FIG. 3 illustrates the selection between the first and second criteria for arrhythmia identification in block / flow format. The method shown in FIG. 3 addresses and prevents delays due to the selection of less sensitive and more conservative criteria for arrhythmia discrimination, and is more aggressive for arrhythmia discrimination when specific signal characteristics are indicated. It is intended to switch to the standard.
In the example, analysis begins with identification of a potential arrhythmia at reference numeral 100. Once a potential arrhythmia is identified at reference numeral 100, the method determines which of the various features, if any, are found in the ongoing heart condition. Using such features, either the more conservative criteria 102 or the more aggressive criteria 104 are applied to make the charging decision 106.
In one example, the potential arrhythmia that triggers the analysis is any rate that exceeds a predetermined threshold. For example, a rate (heart rate) of 150 beats per minute (bpm) may be a threshold that initiates an assessment of whether the arrhythmia discrimination criteria 102 or 104 should be applied. For example, other rates such as a range of 100 to 250 bpm may be selected. Potential arrhythmias can also be identified by shape analysis (morphology), by evaluation of cardiac signals captured within a certain time, by frequency conversion / analysis or other methods. In another example, if an X / Y counter is to be applied, the decision process of FIG. 3 is applied as soon as the most aggressive arrhythmia detection criteria is met. In one such embodiment, the 12/16 X / Y applies to the “aggressive criteria” 104, while the 18/24 X / Y applies to the “conservative criteria” 18 / If either 24 or 12/16 is satisfied, the method of FIG. 3 is performed.
In another approach to “potential arrhythmia” 100, the system may track “promoter” and “inhibitor” counts, and if the “promoter” count exceeds a threshold, block 100 Will be satisfied. Individual blocks on each arm of FIG. 3 can be used for this purpose. For example, any of the blocks 110, 112, 114, 116 may be described as “inhibiting factors”, while the blocks 120, 122, 124 are described as “promoting factors”. The analysis of facilitating and inhibiting factors is performed beat-to-beat basis, so if we focus on two consecutive beats and the interval between them is significantly different from the previous one, A stable interval 122 and / or a sudden onset 124 promotion factor may be counted. As soon as the number of facilitator counts exceeds the number of inhibitor counts, for example, or exceeds some amount or margin, block 100 will be filled.
The option to choose between block 102 and block 104 provides the system with a double reference for arrhythmia identification. In some examples, at least one of the double criteria may also be adaptable, eg, as shown below in FIG.
In the example of FIG. 3, the features of the cardiac signal identified as indicating the application of the more conservative criteria 102 include the identification of “single shape” 110, which is a repetitive cardiac signal and consistent in morphology. Means that An example of identifying a “single shape” 110 signal is that the shape of a QRS complex, R wave, T wave, or other feature of a given detection event is compared to the shape of the same feature of a previous detection event. Evaluation may be included.
Additional features that may be identified in the “single shape” 110 analysis may include amplitude and width alone or a combination thereof. A heart signal has a “single shape” if the shape of the selected feature is approximately the same from one detection event to the next. Alternatively, the shape may be compared to some previous event or average shape. This can also be described as a monomorphic heart signal. In some alternative embodiments, a transform may be used, for example, a Fourier transform, a Laplace transform, a principal component analysis transform or a wavelet transform may be used, or the shape may be determined for the first or second derivative. The shape may be compared from one detection event to the next detection event.
Another feature that has been shown to support the application of more conservative criteria is the spacing stability 112. For example, the interval from one detection event to the next detection event can be compared against the previous interval. If the intervals are similar (eg, within predetermined limits), a stable interval 112 is determined.
Additional features that have been shown to support the application of more conservative criteria include the presence of noise markers 114 and dual detection markers 116. For example, if a threshold number of noise markers 114 or double detection (“DD”) markers 116 is observed within a given period of time or in a predetermined amount of detection events, then the exemplary method is then: Apply more conservative standards. In this example, multiple layers or criteria may be applied. For example, if one noise marker is identified in the previous eight detection events, or three noise markers are identified in the previous 24 detection events, then the example is then “more conservative. “Criteria 102 will apply. In another example, the more conservative criteria 102 may be applied when there are three DD markers in the previous 20 seconds of data. There can be several numerical approaches to the application of the rules of noise marker 114 and DD marker 116.
In the example of FIG. 3, two of the features that support the application of more aggressive criteria include various shapes 120 and unstable spacings 122. These features can be seen when ratings 110 and 112 are respectively negative. Another feature that supports the application of more aggressive criteria is that of sudden onset 124. Sudden onset can be identified if the observed rate of detection events increases rapidly, for example, if the average rate increases from less than 100 bpm to more than 180 bpm in less than 1 second and remains elevated. In an exemplary “sudden onset” assessment, the percent of change from one RR interval to the next RR interval.
criteria) may be applied. Other criteria may be applied.
There are several combinations that can apply to reach one or the other of the reference results 102,104. All or selected subsets of the features 110, 112, 114, 116, 120, 122, 124 shown may be contemplated. Some examples include the following.
In the first embodiment, the heart signal has a variety of shapes (reference number 120 = true and reference number 110 = false) and no noise marker or DD marker has occurred in the last eight events (reference number 114) = False and reference number 116 = false), the more aggressive criteria 104 apply.
In the second embodiment, if any two of the various shapes 120, unstable intervals 122, or sudden onset 124 occur, the more aggressive criterion 104 is applied, otherwise A more conservative standard 102 is applied.
In the third embodiment, any one of the various shapes 120, unstable intervals 122, or sudden onset 124 is more aggressive except when the noise marker 114 or the DD marker 116 is observed. Apply appropriate standards.
In the fourth embodiment, either of the various shapes 120 or the unstable intervals 122 is determined unless the DD marker 116 is observed (in this example, the noise marker 114 has the various shapes 120 or the unstable intervals 122). If not, the more aggressive criteria are applied and the sudden onset 124 is also more aggressive unless the noise marker 114 is observed (in this example, the DD marker does not deny the sudden onset 124). The standard will be applied.
It should be noted that rate is not one of the features that drives the selection of more conservative or more aggressive criteria. Thus, the exemplary approach differs from the layered analysis zones known in the art, where the VT and VF rate zones extend to a lower rate than the VF zone and require morphological analysis of detection events On the other hand, the VF rate zone extending to the highest rate is defined to be a purely rate based decision. US Pat. No. 6,754,528, entitled “APPARATUS AND METHOD OF ARRHYTHMIA DETECTION IN A SUBCUTANEOUS IMPLANT TABLE IMPORTANT CARDIOVERTER / DEFIBRILLATOR” describes an example of a layered zone analysis. The disclosure of said patent document is incorporated herein by reference. In addition, by omitting the rate from consideration of whether conservative criteria or aggressive criteria are selected, the present invention applies separate NID or X / Y criteria, for example, to the VF and VT zones. Different from the example.
In an example, the “more conservative” criteria applied at reference number 102 would be different from the “more aggressive” criteria applied at reference number 104. For example,
A more conservative criterion is a persistence set to 3 and an X / Y counter set to 18/24 is applied, a more aggressive criterion is a persistence set to 2 and 12 / X / Y counter set to 16 is applied.
-For more conservative standards, the X / Y counter set to 30/40 is applied, and for the more aggressive standards, the X / Y counter set to 18/24 is applied. It has no persistence.
The more conservative criteria is a minimum of 2 and a variable persistence that extends if a non-persistent episode occurs, applying an X / Y counter set to 18/24 and more aggressive The standard is a fixed persistence set to 2 and an X / Y counter set to 18/24 is applied. In this example, the 18/24 X / Y counter and persistence may be referred to as default values.
In this last form, FIG. 3 will be useful for extending the X / Y criteria and / or undoing the persistence criteria generated in the example shown in FIG. 2 under selected circumstances. Let's go.
In another example, a combination of multiple criteria can be used to select from conservative criteria, aggressive criteria, or dynamic criteria, as shown below in FIG. In some embodiments, a range of conservative criteria to aggressive criteria may be available to allow the selection of criteria to apply to be made according to cardiac signal characteristics.
In one example, block 100 may correspond to providing an anti-tachycardia pacing therapy. During the delivery of such treatment, a continuous analysis is performed to determine if the system moves to a more aggressive treatment regime. As the device progresses through the progression of treatment decisions, consideration of different criteria of the detected rhythm can be made. In addition, when a sufficient number of factors are identified that support a conservative approach (such as factors 110, 112, 114, 116) when the criteria are applied, existing treatments (such as ATP) The provision of can be terminated.
4-5 show subcutaneous only and transvenous implantable cardiac stimulators. Any implantable heart device may use the methods presented herein, including subcutaneous only implantation as shown in FIG. 4 and transvenous implantation as shown in FIG. Alternatively, epicardial and / or complete intravascular implantation, or intracardiac implantation may be used.
Referring now to FIG. 4, the system is implanted in a patient (most of the anatomical structures other than the patient's heart 150 are not shown), and the container 152 is positioned at the height of the lower breast fold. It is placed near the left axilla. The lead 154 extends centrally toward the xiphoid process and then along the side of the sternum toward the patient's head. It can be seen that the subcutaneous implantation occurs at a location other than the heart 150 and does not contact or enter the heart 150. This avoids various known risks associated with entering or contacting the heart.
Although lead 154 is shown with a plurality of electrodes 156, 158, 160, more or fewer electrodes may be provided. The electrode 160 closest to the xiphoid process is shown as a ring electrode, the central electrode 158 is shown as a coil electrode, and the tip electrode 158 is shown as having a mounting hole. These features and electrode designs can be interchanged, modified, or replaced with any suitable electrode design known in the art. Some exemplary designs include US Pat. No. 8,483,841 entitled “ELECTRODE SPACING IN A SUBCUTANEOUS IMPLANTABLE CARDIAC STIMULUS DEVICE”, and “SUBCUTANOUS LEEADS AND FUNDS AND METHODP AND T U.S. Patent Application Publication No. 2012-0029335. Each of the above patent documents is incorporated herein by reference. Additional examples that could work as well have been shown in numerous other patents and patent applications and / or have been marketed as various types of implantable electrodes or have been marketed in the past.
The container 152 may include electrodes formed as individual electrodes, as part of the surface of the container 152, or as the entire surface of the container 152. The container 152 preferably contains the arithmetic circuitry for the system. The arithmetic circuitry may comprise a controller and any suitable analog and / or digital circuitry required for signal processing, memory retention, and generation of high or low power electrical or non-electrical output. . The arithmetic circuitry may be tied to battery technology suitable for implantable devices having numerous examples well known in the art, and various capacitor technologies may be used for defibrillation or other high power purposes. For this purpose, short-term storage and / or storage of energy may be supported.
In one example, the arithmetic circuitry includes a set of input switches or multiplexers associated with an analog filtering circuitry such as a DC filtering capacitor coupled to an input amplifier. The input amplifier can be associated with additional filtering, such as a bandpass filter, if desired. Where multiple sense vectors are evaluated, there may be more than one input amplifier circuit. The output of the input amplifier may be coupled to the input of an analog-to-digital conversion (ADC) circuitry. The ADC circuitry provides one or more digital signal outputs to a processor or controller. Digital filtering may be performed in the ADC circuitry and / or associated processor or controller.
For example, RAM and / or memory including flash memory or other media can be obtained by the processor / controller to obtain instructions for operation and to store episodes, performance data, signal data, parameter settings, device information, etc. Is accessible. The arithmetic circuitry comprises one or more batteries for powering an implantable system, as well as an output circuit, and in higher power implementations, a capacitor and a filling circuit for generating a defibrillation output from battery power. It can be provided or coupled to one or more batteries. As described above, several commercially available implementations of an apparatus having suitable arithmetic circuitry to perform the present method and / or to be configured to perform such a method. Exists.
The lead 154 and the outer shell of the container 152, along with coatings for such materials, various materials suitable for implantation, such as those widely known throughout the art, and commercially available as indicated above Can be manufactured by the materials used by such equipment. For example, the container may be manufactured using titanium, optionally with a titanium nitride or iridium oxide (or other material) coating, the lead being a polyether, polyester, polyamide, polyurethane or polycarbonate, or silicone rubber. It can be formed by a polymeric material such as other materials. The electrodes 156, 158, 160 may similarly be formed from a suitable material such as silver, gold, titanium or stainless steel such as MP35N alloy, or other materials. The system may have features that allow for use in a magnetic resonance imaging system.
The position of the system insert may vary. For example, the system shown in FIG. 4 is a subcutaneous only system located in the anterior and lateral chest between the patient's skin and rib cage. Other subcutaneous-only systems (including systems without leads 154, including systems with multiple leads 154 or an array of leads 154 in place) are described, for example, in US Pat. Nos. 6,647,292, 6, 721,597, 7,149,575 and 7,194,302, as well as other forward-only arrangements and / or anteroposterior directions, including other positions, Only the rear part can be used in positions such as left and right. Each of the above patent documents is incorporated herein by reference. Subcutaneous placement may include any location between the skin and the rib cage, including under the muscle.
Similarly, a programmer 162 is shown. The programmer 162 and the implantable system are preferably designed to communicate with each other during a programming session. Such communications may include device history and / or status queries, device programming reprogramming, new software / firmware updates or downloads, system testing controls such as inductive testing or pacing testing, lead impedance, or battery measurements It can include values and the like. Although a programmer 162 is shown, it will be appreciated that any suitable monitoring system (such as a home monitoring system) may replace the programmer 162 for any of these functions as desired. As shown, there are various vectors for sensing and / or providing treatment defined by electrodes 156, 158, 160, and can 152.
FIG. 5 shows a transvenous implantation. In this example, the system is implanted in the patient and the patient anatomy other than the heart 180 is not shown. An implantable container 182 is shown and may generally be similar to the container 152 described above in terms of physical characteristics and content (however, specific energy output and signal sensitivity is intended for transvenous applications rather than subcutaneous applications). Can be configured).
Lead 184 is coupled to container 182 and enters the subclavian vein and passes through the vasculature and into heart 180. The lead 184 includes coil electrodes 186a and 186b and ring electrodes 188a and 188b. Alternatively, other means of access to the heart 180 may be used.
The external programmer 190 can be used to communicate with the implanter 182 for a variety of reasons. A plurality of vectors for sensing and / or treatment are defined by electrodes 186a / b, electrodes 188a / b, and containers 182. Alternatively, other implantation locations and approaches may be used, or additional electrodes and leads, or fewer electrodes and leads. There are many commercially available implantable cardiac stimulation and / or monitoring systems with similar or different designs in which examples of the present invention can be implemented by those skilled in the art. Some examples may include dual chamber devices, single chamber devices, biventricular devices, atrial only devices, and the like. Systems with quadrupole or other multipolar leads designed to allow flexible selection of sensing and stimulation electrodes may be used as well.
Some examples include a hybrid / combination with each of implantable defibrillator capabilities and implantable pacemaker capabilities, including implantable defibrillators, implantable pacemakers, and / or cardiac resynchronization therapy devices. It takes the form of such an implantable heart stimulator. Another example may be an implantable heart monitoring device. Implantable cardiac monitoring devices use arrhythmia classification to perform functions such as generating patient alerts, identifying signal data captured for storage, or other suitable functions. It can be determined whether to implement. Some examples may also include the ability to provide pharmaceuticals, neural stimulation / modulation or other suitable treatment. Such a system can be combined with other implantable devices for similar or different purposes, using various known approaches such as RF communications or communications encoded during stimulation output or sub-stimulation output , May be configured to communicate with other implantable devices.
FIG. 6 shows another analysis method in block form. The exemplary method begins at block 200 with identification of a potential arrhythmia. The identification method is described above. Next, the method includes confirming that a treatable arrhythmia 202 is occurring by using an arrhythmia identification parameter or rule and prompting the start of treatment preparation 204. Treatment preparation 204 may include initiating a charging operation on the capacitor to provide a defibrillation stimulus. However, in this example, as shown at reference numeral 206, the shock confirmation later failed, meaning that the identified treatable arrhythmia was not detected before treatment could be provided. For example, the patient's heart rate may fall below the treatable zone. As a result, it is identified that a non-persistent episode 208 has occurred. According to an exemplary method, one or more attributes of an arrhythmia identification parameter or rule are changed at reference numeral 210 in response to identification of a non-persistent episode. These modified parameters are stored for use in later episodes.
A later episode begins again at reference numeral 220 with identification of a potential arrhythmia, followed by selection of an arrhythmia identification rule at reference numeral 222. This selection step 222 may be performed as shown above in FIG. If the condition of the heart rhythm suggests the use of the more conservative modified criteria 224, here the rules modified in block 210, then the modified criteria 224 is then used to determine the reference number 228. Selected at reference numeral 222 for use in the step, the decision step 228 applies the selected arrhythmia identification rule. If instead the heart rhythm status suggests the use of a more aggressive rule, then in this case the default rule is applied unchanged by block 210 and then the default arrhythmia detection rule 226 is in block 228. Applies to judgment.
From the decision block, either the arrhythmia is confirmed and the episode is declared at reference number 230 or the arrhythmia is not confirmed and the system continues sensing as shown at reference number 232. . If an episode is declared at reference number 230, preparation for treatment delivery and final shock confirmation steps may be performed as in blocks 204,206. In the event of another non-persistent episode, the arrhythmia identification rule change at reference number 210 may be repeated within some limits on extension, and the X / Y counter and persistence rules are for a given system. Can be selected.
In this example, the ability to use dual criteria 224, 226 allows for faster identification of arrhythmias in certain situations while retaining the potential benefit of applying more conservative criteria in other situations. obtain. This option also allows the modified criteria 224 to be adaptable to the patient through the use of the change at reference numeral 210.
In another example, the presence of previous episodes can be excluded from the method, and blocks above line 234 are omitted. In this example, the arrhythmia identification rule is automatically selected at reference numeral 222 whenever a potential arrhythmia 220 is identified. In yet another example, following the provision of treatment in a given episode, arrhythmia identification rules may be reselected by observing the characteristics of the detection signal that occurs at that time.
The example of FIG. 6 assumes that the episode declaration occurs at the same time as preparation for treatment delivery, or immediately results in preparation for treatment delivery, but in other examples there is an additional interval between block 202 and block 204. There may be additional steps. For such examples, the episode declaration initiates a first set of activities (episode notification, data storage, ATP, etc.) and provides high-power treatment if arrhythmia continues (ie defibrillation or cardioversion) ) Followed by preparation.
FIG. 7 shows another exemplary embodiment in block form. In this embodiment, a method for selecting an arrhythmia identification parameter is shown and, as shown, three results are possible. Beginning at start block 250, the method may have already made a preliminary presentation of some potential arrhythmias, for example, by determining that an increase in the number of beats has been identified. This preliminary presentation may be omitted from some embodiments.
From block 250, the method determines whether the observed cardiac signal is polymorphic, as indicated by reference numeral 252. For example, the correlation (eg, using correlation waveform analysis, region analysis differences, principal component analysis, wavelet analysis, or other features) of multiple detection events relative to a static or dynamic template may be observed. If such correlation results differ greatly, the shape of the signal is considered polymorphic. Polymorphic rhythm is a higher concern in this embodiment, so if the cardiac signal is found to be polymorphic, a minimum amount of persistence is applied, as shown at reference numeral 262. Then, the method for selecting an arrhythmia identification parameter ends. The method may be repeated for each individual detection event, or a determination may be made for a set of events periodically at set intervals or as desired. One effect of changing the arrhythmia criteria to use the lowest persistence (or other criteria) in response to the identification of the polymorphic arrhythmia may be to reduce the time to treatment. Since polymorphic arrhythmias typically require rapid treatment, this can provide patient benefit.
If the cardiac signal is not polymorphic at reference numeral 252, the method then proceeds to reference numeral 2
A determination is made as to whether the cardiac signal is monomorphic as indicated at 54. In the example of FIG. 7, separate definitions are defined for monomorphism and polymorphism. For example, block 252 finds a series of correlations for static templates that change from one to the next, while block 254 considers a comparison of individual detection events against a dynamic template that updates every beat. If the signal is not monomorphic at reference numeral 254, the current persistence 258 applies. With current persistence 258, the method refers to the persistence requirements defined by the system using its own experience. For example, if the default persistence has been extended in response to a previous non-persistent episode, then the extension will continue to be applied using the “current” persistence. .
Using the definitions in the above example, if the cardiac signal is monomorphic at block 254, the method then determines whether the signal is narrow, as indicated by reference numeral 256. If the signal is not narrow, the method will apply the current persistence at reference numeral 258. On the other hand, if the signal is monomorphic (254) and narrow (256), then the method is maximal before determining that treatment is required, as indicated by reference numeral 260. A persistence value will be applied. In this example, the monomorphism and narrowness of the detected rhythm suggests that the rhythm is not as dangerous as polymorphism or broad arrhythmia.
For example, some monomorphic ventricular tachycardias are well tolerated by the patient, especially when narrow events are observed. Such a feature may refer to exercise-induced ventricular tachycardia that would generally require no treatment. Typically, the physician will select the VT zone rate to accommodate exercise-induced “normal” high rate conditions. However, depending on the patient's condition, short brief excursions of heart rate beyond a defined zone can occur.
In one example with respect to FIG. 7, episodes may be declared before selecting an arrhythmia classification parameter. In this example, start block 250 corresponds to an episode declaration and provides at least data storage for that event. Whether treatment is really required may depend on the application of the selected criteria from FIG.
One difference between FIG. 7 and FIG. 6 is that FIG. 6 shows that the decision of which different arrhythmia criteria to apply is made after at least one non-persistent episode has been identified. Is a point. In FIG. 7 (and likewise in FIG. 8), it is not necessary that a non-persistent episode had previously occurred. Instead, the device simply uses the detected cardiac signal to select from among a plurality of arrhythmia detection criteria that the device can apply.
The example of FIG. 7 uses the morphological evaluation of monomorphism and polymorphism at reference numbers 252 and 254 and merges with the analysis of whether the detection event at reference number 256 is narrow. Other features may be used including, for example, those discussed in US Pat. No. 7,330,757. The disclosure of said patent document is incorporated herein by reference. For example, correlation to a template (any template) may suggest a non-polymorphic signal to which more conservative parameters can be applied. High correlation score variability from one event to the next is more aggressive for treatment decisions, regardless of which template (whether dynamically updated or statically stored) Can suggest a different approach. Both rate acceleration events and low interval stability suggest a more aggressive approach to treatment decisions.
FIG. 8 shows another analysis method. In this way, potential arrhythmias are identified at reference numeral 280. Identification of potential arrhythmias provides an assessment of factors that support the use of active or conservative arrhythmia analysis. Exemplary factors include the similarity of amplitude, width or spectral components between heartbeats, where one or more similarities of these factors favor the use of conservative analysis, while significant differences are more Support active analysis. Additional factors, if present, may include more aggressive analysis, use of correlation analysis (between heartbeats or against templates), rate acceleration to support the presence of noise or overdetection. Another factor may be the presence of an alternating pattern when observing features such as width, correlation, amplitude, frequency component or heart rate interval over three or more detections. The presence of the alternating pattern supports a conservative criterion because they suggest overdetection even if no positive declaration of overdetection is made.
Based on the evaluation of such factors, the example of FIG. 8 follows one of three paths. If the dominant conclusion from the evaluation of several factors supports the conservative criteria, as shown at reference number 282, then the relatively more conservative criteria are applied, as shown at reference number 284. Will. If no prevailing conclusion exists and the factors are considered separated, as shown at reference number 286, then the previous episode history or clinical setting of the system is used, as shown at reference number 288. Dynamic criteria based are applied. If the dominant conclusion from the assessment of several factors supports an aggressive standard as shown at 290, then a relatively more aggressive standard is applied, as shown at 292. Is done.
Next, the criteria selected at reference numbers 284, 288, or 292 are applied to the decision, as indicated at reference number 294. The determination of reference number 294 may be an episode determination, which, for example, or optionally, drives the start of data storage and / or enhanced signal analysis to initiate treatment delivery or high voltage treatment preparation. In an alternative embodiment, the determination of reference number 294 may instead be a determination to begin preparing to provide a high voltage therapy, or a determination to initiate a low voltage therapy such as anti-tachycardia pacing, It is freely made prior to the determination of reference number 294.
In blocks 284 and 292, the example of FIG. By the “more” conservative criterion of reference number 284, the example is changed so that at least one arrhythmia analysis factor does not meet the arrhythmia criterion at least one detection condition that met the arrhythmia criterion before the change. It is shown that. Conversely, at reference numeral 292, the more aggressive application of criteria ensures that at least one arrhythmia analysis factor now meets the arrhythmia criteria, at least one detection state that did not meet the arrhythmia criteria prior to the change. It shows that it is changed.
For example, in the variation of FIG. 8, block 284 applies the most conservative criteria available, for example, allowing the system to use an X / Y counter set to 40/50, which is the maximum Then, block 284 will apply the largest X and Y. Similarly, in this variation, block 292 applies the most aggressive criteria available, for example, allowing the system to use an X / Y counter set to 6/8, which is the lowest available If X and Y, then block 292 will apply the lowest X and Y.
Instead of the three branches shown in FIG. 8, another example applies a gradient as indicated by reference numeral 296. In this example, the extent of the applied criteria change is proportional to the degree to which the factor considered supports the conclusion (aggressive) or others (conservative). The band for evaluation can be determined using the criteria set forth above.
In a further example, the use of “dynamic” criteria is eliminated, and the factors present in identifying potential arrhythmias 280 are used to select from available adjustment slopes to criteria.
In another example, block 294 is a treatment decision block where the criteria selected at reference numbers 284/288/292 are applied. The episode declaration is in this example a predicate for the method and will be included as part of block 280. Thus, an episode or “arrhythmic preliminary declaration” occurs first in block 280 or before block 280, followed by selection of treatment criteria in the manner shown in FIG. Once treatment criteria are selected, the method will move to treatment decisions.
In some embodiments, the indicator used to select the criteria may originate from a source other than the electrical heart signal. For example, a blood pressure monitoring sensor can provide an indication of blood pressure to the system, where very low blood pressure favors the use of more aggressive arrhythmia analysis criteria, and lack of low blood pressure favors the use of more conservative criteria To do. In another embodiment, a cardiac motion sensor, such as a piezoresistor or a piezoelectric element, is placed in a blood vessel associated with the heart or placed in the epicardium or endocardium for input The heart movements that can provide the same may be monitored, and excessively rapid movements or lack of movement both support positive arrhythmia detection criteria. In another example, an oximetry (or other blood component monitoring device) can be used to determine if more aggressive criteria should be applied, in which case blood oxygenation is low Would support the use of more aggressive standards while supporting more conservative standards when blood oxygenation is normal. In yet another embodiment, an accelerometer is provided to allow for the identification of sudden changes in position (possibly indicating that the patient has fallen) and the presence of data from the accelerometer that suggests that a fall has occurred. Will be used to select positive criteria.
Another set of examples allows an implantable defibrillator with the ability to detect an RF signal in response to identifying potential arrhythmias. Upon receiving an RF signal generated in response to the identified treatable condition from one or more other implantable systems, the defibrillator will then select a more aggressive arrhythmia detection criterion. Let's go. For example, an implantable subcutaneous defibrillator may co-exist with an implantable leadless space maker (US Patent Publication No. 20110208260). Through its detection method, the leadless space maker can identify that the heart rate is higher than a preset limit, and then, for example, using RF communications or sonic output or by specially shaped pacing output Will start sending alerts. Once the subcutaneous ICD identifies a potential arrhythmia, it will begin observing whether any communication is being generated by the leadless space maker. The reception or identification of such communication will then cause the subcutaneous ICD to modify its detection parameters. This would allow the subcutaneous ICD to independently verify the arrhythmia while still allowing the leadless space maker to play a role. In another example, a pulse oximeter or blood pressure monitoring device will provide the output signal.
In another example, a blood component monitoring device or blood pressure monitoring device may be polled by an implantable device. For example, the RFID circuitry may be integrated into a blood oxygenation or blood pressure monitoring device. In that case, the RFID output embeds features that indicate the state of blood oxygenation or pressure. If the cardiac treatment system identifies a potential arrhythmia, the system generates an output that polls the RFID device, and whether the monitored oxygenation or pressure is in a range that indicates the need for immediate treatment Judging. If so, then the more aggressive parameters will apply.
A first embodiment includes an arithmetic circuit arrangement configured to couple to a sensing electrode to sense cardiac activity, detect an event in the sensed cardiac activity, and provide therapy in response to the identified condition It takes the form of an implantable heart stimulator provided. The arithmetic circuit configuration is configured to use one or more arrhythmia identification parameters that can be changed within a predetermined range. In this first embodiment, the arithmetic circuit configuration uses a set of detection events to establish a preliminary identification of potentially treatable arrhythmias, and using predetermined parameters, the set of detection events can be varied. If the set of detection events has a variety of shapes, a preliminary identification of the potentially treatable arrhythmia is treated. Apply a first value to the arrhythmia detection parameter to evaluate whether it should be declared as a possible arrhythmia episode, and if the set of detection events does not have various shapes, the potential Configured to apply a second value to the arrhythmia detection parameter to assess whether a pre-identification of the treatable arrhythmia should be declared as a treatable arrhythmia episode Cage, the second value different from the first value.
In a second embodiment, the arithmetic circuitry identifies a potentially treatable non-persistent episode of arrhythmia, changes the second value for the arrhythmia detection parameter accordingly, and sets the second value for the arrhythmia detection parameter. A first embodiment is incorporated that is further configured to set a value to a predetermined default value for the altered arrhythmia detection parameter.
A third embodiment takes the form of an implantable cardiac stimulator with computing circuitry configured to couple to sensing electrodes to sense cardiac activity and detect events in the cardiac activity, The computing circuitry is further configured to provide therapy in response to the identified condition. In this third embodiment, the arithmetic circuit configuration observes the characteristics of the cardiac signal of the set of detected events and uses the observed characteristics to at least a first set of arrhythmia declaration parameters and a second of the arrhythmia declaration parameters. Select from among the sets, where for at least the detected set of data, analysis using the first set of arrhythmia declaration parameters does not declare a treatable arrhythmia, but using the second set of arrhythmia declaration parameters As the analysis declares a treatable arrhythmia, the first set of arrhythmia declaration parameters is different from the second set of arrhythmia declaration parameters, and cardiac activity sensed using the selected set of arrhythmia declaration parameters. Is configured to analyze. In a variation of this third embodiment, the arithmetic circuitry also uses a set of detection events to establish a pre-identification of a potentially treatable arrhythmia before selecting from among arrhythmia detection parameters. It may be configured.
In the fourth embodiment, the arithmetic circuit configuration observes the characteristics of the heart signal of the set of detected events in order to select from the first set and the second set of arrhythmia declaration parameters without observing heart rate information. The third embodiment is further configured to be configured. Instead, the arithmetic circuitry in this fourth embodiment is configured to analyze other features. Some such other features are shown in the examples below.
In a fifth embodiment, the arithmetic circuit configuration is further configured to observe characteristics of the cardiac signal of the set of detected events by determining whether a monomorphic cardiac signal is occurring. Three examples are incorporated. In a sixth embodiment, the arithmetic circuitry is further configured to select a first set of arrhythmia declaration parameters in response to a determination that a monomorphic heart signal is occurring. Incorporate an example. In a seventh embodiment, the arithmetic circuitry is further configured to select a second set of arrhythmia declaration parameters in response to a determination that no monomorphic heart signal is occurring. Incorporate an example.
In the eighth embodiment, the arithmetic circuit configuration determines whether the interval defined between the detection events in the detection event set is stable, thereby observing the characteristics of the heart signal of the detection event set. Incorporating the third embodiment. The ninth embodiment incorporates an eighth embodiment, wherein the arithmetic circuitry is further configured to select a first set of arrhythmia declaration parameters in response to a determination that the interval is stable. . The tenth embodiment is further configured to select the second set of arrhythmia declaration parameters in response to the determination that the arithmetic circuit configuration is not stable, the eighth embodiment Include.
The eleventh embodiment is further configured to analyze individual detection events in order to identify whether any detection is occurring due to noise, and the calculation circuit configuration includes the detection circuit configuration. Incorporating a third example, the step of observing the cardiac signal characteristics of the set of events is configured to include determining whether one or more detections have been identified as noise. In a twelfth embodiment, the arithmetic circuitry is configured to select a first set of arrhythmia declaration parameters in response to a determination that one or more detections have been identified as noise. Incorporate an example. The thirteenth embodiment is further configured to select the second set of arrhythmia declaration parameters in response to a determination that the arithmetic circuitry is not detected identified as noise. Include.
The fourteenth embodiment is further configured to analyze each detection event in order to identify whether the arithmetic circuit configuration has some detection due to overdetection, and the arithmetic circuit configuration includes Incorporating a third embodiment, the step of observing a cardiac signal characteristic of the set of detection events is configured to include determining whether one or more detections have been identified as overdetection. In a fifteenth embodiment, the arithmetic circuitry is configured to select a first set of arrhythmia declaration parameters in response to a determination that one or more detections have been identified as overdetected. The 14th embodiment is incorporated. The sixteenth embodiment is further configured to select the second set of arrhythmia declaration parameters in response to the determination that the arithmetic circuitry is not detected as overdetected. Incorporate
In a seventeenth embodiment, the arithmetic circuit configuration is further configured to observe features of the cardiac signal of the set of detected events by determining whether a sudden onset of an increase in heart rate has occurred. Three examples are incorporated. In an eighteenth embodiment, the arithmetic circuitry is further configured to select a first set of arrhythmia declaration parameters in response to a determination that no sudden onset of heart rate increase has occurred. Examples are incorporated. In a nineteenth embodiment, the arithmetic circuitry is further configured to select a second set of arrhythmia declaration parameters in response to a determination that a sudden onset of increased heart rate has occurred. Examples are incorporated.
The twentieth embodiment takes the form of a method for cardiac signal analysis in an implantable heart device. The implantable heart device includes electrodes coupled to arithmetic circuitry to sense cardiac activity and perform cardiac signal analysis, the method being potentially treatable using a set of detection events Establishing a preliminary identification of the arrhythmia, observing the cardiac signal characteristics of the set of detected events, and using the observed characteristics, selecting from a first set of arrhythmia declaration parameters and a second set of arrhythmia declaration parameters. And, for at least the detected set of data, analysis using the first set of arrhythmia declaration parameters does not declare treatable arrhythmia, but analysis using the second set of arrhythmia declaration parameters is treatable The first set of arrhythmia declaration parameters is different from the second set of arrhythmia declaration parameters so as to declare an arrhythmia.
A twenty-first embodiment includes an arithmetic circuit arrangement configured to couple to a sensing electrode to sense cardiac activity, detect an event in the sensed cardiac activity, and provide therapy in response to the identified condition It takes the form of an implantable heart stimulator provided. The arithmetic circuit configuration is configured to use one or more arrhythmia identification parameters that can be changed within a predetermined range. In this twenty-first embodiment, the arithmetic circuitry comprises the means for establishing a pre-identification of a potentially treatable arrhythmia using a set of detection events and a set of detection events using predetermined parameters. A determination means for determining whether the set has a variety of shapes or a consistent shape; and if the set of detection events has a variety of shapes, a potentially treatable arrhythmia A first value applying means configured to apply a first value to an arrhythmia detection parameter to assess whether the preliminary identification should be declared as a potentially treatable arrhythmia episode; If the set of events does not have a variety of shapes, evaluate whether a preliminary identification of a potentially treatable arrhythmia should be declared as a potentially treatable arrhythmia episode In order, and a second value applying means configured to apply a second value for arrhythmia detection parameters, the second value different from the first value.
A twenty-second embodiment takes the form of an implantable cardiac stimulator with computing circuitry configured to couple to sensing electrodes to sense cardiac activity and detect events in the cardiac activity, The computing circuitry is further configured to provide therapy in response to the identified condition, the computing circuitry using a set of detection events to establish a preliminary identification of potentially treatable arrhythmias. And an observing means for observing characteristics of the cardiac signal of the set of detection events and using the observed characteristics to select from a first set of arrhythmia declaration parameters and a second set of arrhythmia declaration parameters. An analysis using the first set of arrhythmia declaration parameters does not declare a treatable arrhythmia, at least for the detected set of data, but the arrhythmia declaration Analysis using the second set of parameters is to declare a treatable arrhythmia, said first set of arrhythmia declaration parameters are conservative than the second set of arrhythmia declaration parameters.
Each of these non-limiting examples may be independent or may be combined with one or more of the other examples in various permutations or combinations. Some of these embodiments may be embodied in an implantable pulse generator configured for use with an implantable lead having a sensing electrode thereon. Other embodiments may be embodied in a system that includes both an implantable pulse generator and a lead having a sensing electrode.
The above detailed description includes references to the accompanying drawings, which form a part of the detailed description. The drawings show, by way of illustration, specific embodiments in which the invention can be practiced. These embodiments are also referred to herein as “examples”. Such embodiments may include elements in addition to those shown or described. However, the inventors also contemplate embodiments in which only those elements shown or described are provided. In addition, the inventors have also discussed certain embodiments (or one or more aspects thereof) shown or described herein, or other embodiments (or one or more aspects thereof). In any regard, embodiments using any combination or permutation of those elements shown or described (or one or more aspects thereof) are also contemplated.
In the event of a usage discrepancy between this document and a document so incorporated by reference, the usage of this document will control.
In this document, the term “a” or “an” is any common example of “at least one” or “one or more” as common in the patent literature. Or, regardless of usage, it is used to include one or more. In this document, the term “or”, unless otherwise indicated, “A or B” includes “A but not B”, “B but not A”, and “A and B”. , Used to indicate non-exclusive OR. In this document, the terms “including” and “in which” are used as plain English equivalents of the terms “comprising” and “where”. It is done. Also, in the following claims, the terms “including” and “comprising” are non-limiting, that is, include elements in addition to those listed after such terms in the claims. A system, apparatus, article, composition, formulation or process is still considered to be within the scope of the claims. Further, in the following claims, the terms “first”, “second”, “third”, etc. are used merely as labels and impose numerical requirements on their objects. Is not intended.
The example methods described herein may be implemented at least in part by a machine or a computer. Some examples include computer readable media or machine readable media encoded with instructions operable to configure an electronic device to perform a method as described in the above examples. Examples of performing such methods may include code such as microcode, assembly language code, high level language code, and the like. Such code may include computer readable instructions for performing various methods. The code may form part of a computer program product. Further, in one example, the code may be specifically stored on one or more volatile, non-transitory or non-volatile tangible computer readable media, for example during execution or at other times. Examples of these tangible computer readable media include hard disks, removable magnetic disks, removable optical disks (eg, compact disks and digital video disks), magnetic cassettes, memory cards or memory sticks, random access memory (RAM), read only memory (ROM). However, it is not limited to these.
The above description is intended to be illustrative and not restrictive. For example, the above-described examples (or one or more aspects thereof) may be used in combination with each other. Other embodiments can be used, for example, by one of ordinary skill in the art upon review of the above description. The abstract is provided to comply with 37 CFR 1.72 (b) so that the reader can quickly ascertain the nature of the technical disclosure. It is submitted with the understanding that it will not be used to interpret or limit the scope or meaning of the claims. Also, in the above detailed description, various features may be grouped to simplify the disclosure. This should not be interpreted as intending that an unclaimed disclosed feature is essential to any claim. Rather, the subject matter of the invention may be less than all the features of a particular disclosed embodiment. Thus, the following claims are hereby incorporated into the detailed description as examples or embodiments, with each claim standing on its own as a separate embodiment. It is also contemplated that such embodiments may be combined with each other in various combinations or permutations. The scope of the invention should be determined with reference to the appended claims, along with the full scope of equivalents to which such claims are entitled.
In an implantable cardiac stimulator comprising sensing electrodes coupled to computing circuitry for sensing cardiac activity, detecting an event in the sensed cardiac activity, and providing therapy in response to the identified condition, the computing The circuit configuration is configured to use one or more arrhythmia identification parameters that can be changed within a predetermined range, and the arithmetic circuit configuration includes:
A determination means for determining whether the set of detection events has various shapes or a consistent shape by using predetermined parameters;
In order to evaluate whether a pre-identification of a potentially treatable arrhythmia should be declared as a potentially treatable arrhythmia episode if the set of detection events has a variety of shapes, First value applying means configured to apply a first value to the arrhythmia detection parameter;
If the set of detection events does not have a variety of shapes, then to evaluate whether a preliminary identification of a potentially treatable arrhythmia should be declared as a potentially treatable arrhythmia episode Second value applying means configured to apply the second value to the arrhythmia detection parameter,
The implantable heart stimulator wherein the second value is different from the first value.
An implantable cardiac stimulator comprising electrodes coupled to an arithmetic circuitry for sensing cardiac activity and detecting an event in the cardiac activity, the arithmetic circuitry configured to treat in response to the identified condition The arithmetic circuit configuration is further configured to provide:
Observe the features of the cardiac signal of the set of detection events, and use the observed features, at least
a) a first set of arrhythmia declaration parameters;
b) including an observation means for selecting from a second set of arrhythmia declaration parameters;
At least for the detected set of data, the analysis using the first set of arrhythmia declaration parameters does not declare a treatable arrhythmia, but the analysis using the second set of arrhythmia declaration parameters declares a treatable arrhythmia And wherein the first set of arrhythmia declaration parameters is more conservative than the second set of arrhythmia declaration parameters.
3. The implantable cardiac stimulator of any one of claims 1-2, further comprising establishment means for establishing a preliminary identification of potentially treatable arrhythmias using a fixed number of detection events.
4. The observation means according to any one of the preceding claims, wherein the observation means is arranged to operate without considering the rate of cardiac events to select from the set of arrhythmia declaration parameters. Implantable heart stimulator.
Implantation according to any of the preceding claims, wherein the observation means is arranged to evaluate the interval stability between detection events in order to select from the set of arrhythmia declaration parameters. Type heart stimulator.
6. Implantable implant according to any one of the preceding claims, wherein the observation means is arranged to evaluate a sudden onset of a rapid rate to select from the set of arrhythmia declaration parameters. Heart stimulator.
Whether the sensed cardiac signal and / or detected event further includes noise identifying means for identifying whether the noise event is observed for selecting from the set of arrhythmia declaration parameters. The implantable cardiac stimulating device according to any one of claims 1 to 6, wherein the implantable cardiac stimulating device is configured to take into account.
Over-detection means for identifying whether a detection event is caused by over-detection, wherein the observation means evaluates whether over-detection is observed to select from among the set of arrhythmia declaration parameters The implantable cardiac stimulating device according to any one of claims 1 to 7, which is configured.
JP2016501042A 2013-03-11 2014-03-10 Method and apparatus for realizing a dual reference for arrhythmia detection Pending JP2016512460A (en)
US201361776326P true 2013-03-11 2013-03-11
US61/776,326 2013-03-11
JP2016512460A true JP2016512460A (en) 2016-04-28
JP2016501042A Pending JP2016512460A (en) 2013-03-11 2014-03-10 Method and apparatus for realizing a dual reference for arrhythmia detection
EP (1) EP2967404B1 (en)
CN (1) CN105208928B (en)
DE3853817D1 (en) 1987-09-02 1995-06-22 Telectronics Pty Ltd Reconfirmation before the shock of an implantable defibrillation.
CA2296545A1 (en) 1997-07-17 1999-01-28 Cpr Medical, Inc. Defibrillator/pacemaker
JP5308443B2 (en) 2007-08-23 2013-10-09 キャメロン ヘルス、 インコーポレイテッド Screening kit and patient screening device for embedded cardiac stimulation system
CA2717446C (en) 2008-03-07 2016-10-25 Cameron Health, Inc. Methods and devices for accurately classifying cardiac activity
2014-03-10 WO PCT/US2014/022713 patent/WO2014164530A1/en active Application Filing
2014-03-10 EP EP14714520.5A patent/EP2967404B1/en active Active
2014-03-10 JP JP2016501042A patent/JP2016512460A/en active Pending
2014-03-10 CN CN201480027181.5A patent/CN105208928B/en active IP Right Grant
2014-03-10 US US14/203,121 patent/US9149645B2/en active Active
2015-09-11 US US14/851,138 patent/US9421390B2/en active Active
2016-07-26 US US15/219,437 patent/US9844678B2/en active Active
US9844678B2 (en) 2017-12-19
WO2014164530A1 (en) 2014-10-09
US20160001089A1 (en) 2016-01-07
US9149645B2 (en) 2015-10-06
EP2967404A1 (en) 2016-01-20
CN105208928A (en) 2015-12-30
US9421390B2 (en) 2016-08-23
US20140257421A1 (en) 2014-09-11
CN105208928B (en) 2018-10-19
US20160331985A1 (en) 2016-11-17
EP2967404B1 (en) 2019-05-22
CA2527558C (en) 2014-11-04 Method and devices for performing cardiac waveform appraisal
JP4977030B2 (en) 2012-07-18 Arrhythmia classification system
2017-01-11 A02 Decision of refusal