Source: https://patents.google.com/patent/WO2004012815A1/en
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WO2004012815A1 - Systems predicting congestive heart failure - Google Patents
Systems predicting congestive heart failure Download PDF
WO2004012815A1
WO2004012815A1 PCT/US2003/024597 US0324597W WO2004012815A1 WO 2004012815 A1 WO2004012815 A1 WO 2004012815A1 US 0324597 W US0324597 W US 0324597W WO 2004012815 A1 WO2004012815 A1 WO 2004012815A1
PCT/US2003/024597
2002-08-06 Priority to US10/213,268 priority Critical patent/US7127290B2/en
2002-08-06 Priority to US10/213,268 priority
2003-08-06 Application filed by Cardiac Pacemakers, Inc. filed Critical Cardiac Pacemakers, Inc.
2004-02-12 Publication of WO2004012815A1 publication Critical patent/WO2004012815A1/en
206010000060 Abdominal distension Diseases 0 claims 1
206010007559 Cardiac failure congestive Diseases 0 abstract claims description title 216
208000006029 Cardiomegaly Diseases 0 claims description 2
206010011224 Cough Diseases 0 claims description 8
208000000059 Dyspnea Diseases 0 claims description 11
206010013975 Dyspnoeas Diseases 0 claims description 11
206010019842 Hepatomegaly Diseases 0 claims description 6
206010030124 Oedema peripheral Diseases 0 claims description 4
206010031123 Orthopnoea Diseases 0 claims description 5
208000002151 Pleural Effusion Diseases 0 claims description 7
208000005333 Pulmonary Edema Diseases 0 claims description 2
230000000747 cardiac Effects 0 claims description 50
201000006233 congestive heart failure Diseases 0 abstract claims description title 216
230000010247 heart contraction Effects 0 claims description 9
230000033764 rhythmic process Effects 0 claims description 44
SYSTEMS PREDICTING CONGESTIVE HEART FAILURE
This patent application is a continuation-in-part of Sweeney et al. U.S. Patent Application Serial Number 09/850,537, filed on May 7, 2001, entitled "CARDIAC RHYTHM MANAGEMENT SYSTEM WITH ARRHYTHMIA PREDICTION AND PREVENTION," which is, in rum, a continuation of Sweeney et al. U.S. Patent Application Serial Number 09/411,345, filed on October 1, 1999, and issued on August 7, 2001 as U.S. Patent No. 6,272,377, each of which is assigned to Cardiac Pacemakers, Inc., the specification of each which is incorporated herein by reference in its entirety.
This document relates generally to medical systems, devices, and methods, and particularly, but not byway of limitation, to cardiac rhythm management systems and methods for congestive heart failure.
One problem faced by physicians treating cardiovascular patients is the treatment of congestive heart failure (also referred to as "CHF"). Congestive heart failure, which can result from long-term hypertension, is a condition in which the muscle in the walls of at least one of the right and left sides of the heart deteriorates. By way of example, suppose the muscle in the walls of left side of the heart deteriorates. As a result, the left atrium and left ventricle become enlarged, and the heart muscle displays less contractility. This decreases cardiac output of blood through the circulatory system which, in turn, may result in an increased heart rate and less resting time between heartbeats. The heart consumes more energy and oxygen, and its condition typically worsens over a period of time.
C rdiac rhythm management systems include, among other things, pacemakers, also referred to as pacers. Pacers deliver timed sequences of low energy electrical stimuli, called pace pulses, to the heart, such as via an intravascular lead wire or catheter (referred to as a "lead") having one or more electrodes disposed in or about the heart. Heart contractions are initiated in response to such pace pulses (this is referred to as "capturing" the heart). By properly timing the delivery of pace pulses, the heart can be induced to contract in proper rhythm, greatly improving its efficiency as a pump. Pacers are often used to treat patients with bradyanhythmias, that is, hearts that beat too slowly, or irregularly. Such pacers may also coordinate atrial and ventricular contractions to improve pumping efficiency.
Cardiac rhythm management systems also include cardiac ^synchronization therapy (CRT) devices for coordinating the spatial nature of heart depolarizations for improving pumping efficiency, such as for patients having CHF. For example, a CRT device may deliver appropriately timed pace pulses to different locations of the same heart chamber to better coordinate the contraction of that heart chamber, or the CRT device may deliver appropriately timed pace pulses to different heart chambers to improve the manner in which these different heart chambers contract together. Cardiac rhythm management systems also include defibrillators that are capable of delivering higher energy electrical stimuli to the heart. Such defibrillators include cardioverters, which synchronize the delivery of such stimuli to sensed intrinsic heart activity signals. Defibrillators are often used to treat patients with tachyarrhythmias, that is, hearts that beat too quickly. Such too-fast heart rhythms also cause diminished blood circulation because the heart isn't allowed sufficient time to fill with blood before contracting to expel the blood. Such pumping by the heart is inefficient. A defibrillator is capable of delivering a high energy electrical stimulus that is sometimes referred to as a defibrillation countershock, also referred to simply as a "shock." The countershock interrupts the tachyarrhytl mia, allowing the heart to reestablish a normal rhythm for the efficient pumping of blood, hi addition to pacers, CRT devices, and defibrillators, cardiac rhythm management systems also include devices that combine these functions, as well as monitors, drug delivery devices, and any other implantable or external systems or devices for diagnosing or treating the heart.
Figure 1 is a schematic diagram illustrating generally, by way of example, but not byway of limitation, portions of a cardiac rhythm management system capable of predicting future congestive heart failure (CHF) status.
Figure 2 is a graph illustrating generally, by way of example, but not by way of limitation, various CHF physiological parameters, at least two of which are used in the probability computation to provide a weighted probability of a CHF status change occurring during a predetermined future time period.
In this document, the terms "a" or "an" are used, as is common in patent documents, to include one or more than one. Furthermore, all publications, patents, and patent documents referred to in this document are incorporated by reference herein in their entirety, as though individually incorporated by reference. In the event of inconsistent usages between this documents and those documents so incorporated by reference, the usage in the incorporated reference(s) should be considered supplementary to that of this document; for irreconcilable inconsistencies, the usage in this document controls.
This document discusses, among other things, systems, devices, and methods that will be described in applications involving implantable medical devices including, but not limited to, implantable cardiac rhythm management systems such as pacemakers, cardioverter/defibrillators, pacer/defibrillators, biventricular or other multi-site resynchromzation or coordination devices, and drug delivery systems. However, these systems, devices, and methods may be employed in unimplanted devices, including, but not limited to, external pacemakers, cardioverter/ defibrillators, pacer/defibrillators, biventricular or other multi-site resynchromzation or coordination devices, monitors, programmers and recorders, whether such devices are used for providing a diagnostic, a therapy, or both a diagnostic and a therapy.
Figure 1 is a schematic diagram illustrating generally, by way of example, but not by way of limitation, portions of a cardiac rhythm management system 1O0 capable of predicting future congestive heart failure (CHF) status. In this example, system 100 includes a hermetically sealed implantable cardiac rhythm management device 105 and a programmer or other external user interface 110. In this example, intracardiac leads 115 A-B are catheters connected to device 105, with respective distal portions intravascularly introduced into heart 120. In the illustrative example of Figure 1, a distal portion of lead 115A is introduced into a right ventricle of heart 120, and a distal portion of lead 115B is introduced through coronary sinus 125 (which, in this document, includes the great cardiac vein) into proximity with a wall of a left ventricle of heart 120. h this example, leads 115A-B each include one or more pacing and/or defibrillation electrodes, e.g., 117A-B, such as for providing pacing, resynchromzation (e.g., for a CHF subject), cardio version, and/or defibrillation therapy to heart 120. hi the example of Figure 1, device 105 carries various electrical components, such as a communication circuit 130, which is capable of wirelessly communicating with a communication circuit of nearby remote external user interface 110. hi another example, communication circuit 130 is capable of wirelessly communicating with a communication circuit of a distant remote external user interface 199, such as by using a nearby external communication repeater 196. In one example, repeater 196 is coupled to user interface 199 via internet connection 197. hi another example, repeater 1 6 also communicatively couples device 105 to an electronic medical database 198, such as via internet connection 197. In a further example, communication circuit 130 of device 105 is communicatively coupled to a communication circuit of a weight scale or other external sensor 135. In one example, device 105 additionally or alternatively includes an implantable sensor 140 therewithin or implanted nearby and coupled thereto. For predicting a future change in a subject's CHF status, system 100 includes a CHF physiological parameter input device 145 and a processor 150 for performing the prediction by computing a weighted probability using at least two CHF physiological parameters obtained from CHF parameter input device 145, thereby increasing the accuracy of the future CHF status change prediction. CHF parameter input device 145 includes one or more of external sensor(s) 135, nearby external user interface 110, distant external user interface 199, computerized patient information medical database 198, and/or implantable sensor(s) 140. In one example, device 105 also includes a therapy control module 155, which uses an indication of the predicted probability of a CHF status change occurring within a predetermined future time period as at least one factor for adjusting a therapy provided by pulse generator circuit 160 through electrodes 117A-B to heart 120. In another example, device 105 communicates an indication of the predicted probability of a CHF status (or derived therefrom) to nearby external user interface 110 and or more distant external user interface 199 to be provided to a physician, caregiver, patient, or other user.
In the example of Figure 1, processor 150 is capable of sequencing through various control states such as, for example, by using a digital microprocessor having executable instructions stored in an associated instruction memory circuit, a microsequencer, or a state machine. However, processor 150 is capable of using many other hardware/firmware/software implementations. In the example of Figure 1, processor 150 includes an on-board or off-board memory circuit 165, which is capable of storing data associated with at least two CHF physiologic parameters (e.g., CHF Parameter 1, CHF Parameter 2, . . ., CHF Parameter N) and conesponding conditional probabilities or other weights associated with each such parameter (e.g., Weight 1, Weight 2, . . . , Weight N). In general, each weight is computed using historical data relating the corresponding CHF physiologic parameter to CHF status, hi one example, the historical data is obtained from the same subject from which the CHF physiologic information is obtained. In another example, the historical data is obtained from at least one different subject (for example, by accessing data in medical database 198). In a further example, the historical data is obtained from a population of subjects. Processor 150 also includes a CHF status change module 170, which may be implemented either in dedicated hardware or as a sequence of instructions executed by processor 150.
In another example, a weight is computed using not only its corresponding CHF physiologic parameter, but also using information about which other CHF physiologic parameter (and/or how many other CHF physiologic parameters) are also being used to predict the likelihood of a change in the subject's CHF status. In an illustrative example, suppose parameters A and B each have weights of 0.1, leading to a combined prediction weight of 0.2. In another example, however, parameters A and B each have weights of 0.1 , when these parameters are individually used in the CHF status change prediction, but have a different (e.g., greater or lesser) weight when both are present (e.g., a stronger weight of 0.5 when both A and B are sufficiently present and used in the CHF status change prediction. Therefore, the weight values may depend on cross-correlation between two or more different CHF physiologic parameters. In one example, a matrix is used to store the weights, and the matrix index is used to access the particular weights that are appropriate for a particular combination of CHF physiologic parameters, hi another example, the weight values depend on how many CHF physiologic parameters are being used to compute the likelihood of a subject's CHF status change. As an illustrative example, suppose CHF physiologic parameter A has a weight of 0.5 when it is used alone for predicting a subject's CHF status change. In another example, however, CHF physiologic parameter has a weight of 0.25 when used in combination with one other different CHF physiologic parameter (e.g., parameter B or parameter C, etc.).
In the example of Figure 1, CHF status change module 170 includes a probability computation module 172 that computes a probability of the subject undergoing a change in CHF status using the weighted probability of the at least two CHF physiologic parameters. An indication of the computed probability is output at node 175 and input to comparator 180, which compares it to a predetennined threshold that is also input to comparator 180. The resulting comparison, which is stored at prediction storage location 185, provides a binary indication of whether the predicted change in CHF status is deemed significant. In one example, either this binary indication at node 190 of whether the predicted CHF status change is significant, or the underlying probability of a change in CHF status at 195 is provided to therapy control module 155, which responsively adjusts one or more therapy parameters controlling how pulse generator circuit 160 delivers therapy to heart 120. Either or both of the status indicators at 175 and/or 190 can also be communicated via nearby user interface 110 and/or more distant user interface 199.
Figure 2 is a graph illustrating generally, by way of example, but not by way of limitation, various CHF physiological parameters 200A-S, at least two of which are used in the probability computation 205 to provide a weighted probability at 210 of a CHF status change occurring during a predetermined future time period. The probability at 210 is computed by normalizing an indication of each of the two or more CHF physiological parameters 200A-S (to obtain P,) and scaling each such normalized CHF physiological parameter 200A- S by its corresponding weight, ,-, and summing the resulting products.
In another example, the subject's weight is used as a CHF physiologic parameter 200B. hi one example, the subject's weight is measured by an external sensor 135 having a scale coupled to a wireless cornmunication circuit that is capable of communicating with communication circuit 130 in implantable device 105. In another example, the subject's weight is measured on an external scale, and manually input by the subject, caregiver, or another user to nearby external user interface 110, and wirelessly communicated to communication circuit 130 of implantable device 105. An increase in weight correlates to a future worsening of the subject's CHF status during the predetermined future time period. h another example, the subject's shortness of breath while sleeping (i.e., paroxysmal nocturnal dyspnea) is used as a CHF physiologic parameter 200C. In one example, paroxysmal nocturnal dyspnea is measured by implantable sensors 140 including a respiration sensor (e.g., an impedance sensor) to detect the shortness of breath and a sleep detector. One example of a sleep detector is described in Carlson et al. U.S. Patent Application Serial No. 09/802,316, entitled "CARDIAC RHYTHM MANAGEMENT SYSTEM USING TIME-DOMAIN HEART RATE VARIABILITY INDICIA," which is assigned to Cardiac Pacemakers, inc., and which is incorporated herein by reference in its entirety, including its description of a sleep detector. In another example, the subject, caregiver, or another user enters an indication of the degree of paroxysmal nocturnal dyspnea into nearby external user interface 110 of CHF parameter input device 145. An increase in paroxysmal nocturnal dyspnea correlates to a future worsening of the subject's CHF status during the predetermined future time period.
In another example, the subject's shortness of breath while lying down, i.e., orthopnea, is used as a CHF physiologic parameter 200D. In one example, orthopnea is measured by implantable sensors 140 including a respiration sensor (e.g., an impedance sensor) to detect the shortness of breath and a posture sensor (e.g., an accelerometer). In another example, the subject, caregiver, or another user enters an indication of the degree of orthopnea into external user interface 110 of CHF parameter input device 145. An increase in orthopnea correlates to a future worsening of the subject's CHF status during the predetermined future time period. In another example, the subject's changed respiration sounds (e.g., increased rales) is used as a CHF physiologic parameter 200E. In one example, the changed respiration sounds are measured by implantable sensor 140 including a microphone, accelerometer, or other like sound detector. In another example, the subj ect, caregiver, or another user enters an indication of the degree of increased rales into external user interface 110 of CHF parameter input device 145. An increase in rales correlates to a future worsening of the subject's CHF status during the predetermined future time period.
In another example, the subject's heart sounds (for example, heart sounds refened to in the art as S1? S2, and particularly the heart sound refened to in the art as S3) are used as a CHF physiologic parameter 200F. In one example, the heart sounds are measured by implantable accelerometer or other sensor 140, such as by using the systems and methods described in Lincoln et al. U.S. Patent Application Serial Number 09/862,763, entitled "CARDIAC RHYTHM MANAGEMENT SYSTEM SELECTING A-V DELAY BASED ON INTERVAL BETWEEN ATRIAL DEPOLAPJZATION AND MITRAL
VALVE CLOSURE," and/or the systems and methods described in Lincoln et al. U.S. Patent Application Serial Number 10/099,865, entitled "CARDIAC RHYTHM MANAGEMENT SYSTEM AND METHOD USING TIME BETWEEN MITRAL VALVE CLOSURE AND AORTIC EJECTION," each of which is assigned to Cardiac Pacemakers, Inc., and the disclosure of each of which is incorporated herein by reference in its entirety, including its description of heart sound detection. An increase in certain heart sounds (e.g., S3) correlates to a future worsening of the subject's CHF status during the predetermined future time period.
In another example, the subject's neck vein distension (e.g., bulging neck vein) is used as a CHF physiologic parameter 200G. In one example, the subject, caregiver, or another user enters an indication of the degree of neck: vein distension into external user interface 110 of CHF parameter input device 145. An increase in neck vein distension correlates to a future worsening of the subject's CHF status during the predetermined future time period.
In another example, the subject's abdominojugular reflex (e.g., bulging of neck vein upon applying compression to the subject's thorax) is used as a CHF physiologic parameter 2O0H. In one example, the subject, caregiver, or other user enters an indication of the degree of abdominojugular reflex into external user interface 110 of CHE parameter input device 145. An increase in abdominojugular reflex coreelates to a future worsening of the subject's CHF status during the predetermined time period.
In another example, the subject's cardiomegaly (i.e., enlargement of heart) is used as a CHF physiologic parameter 2001. hi one example, the subject's heart size is measured by implantable sensor 140 (e.g., a transthoracic impedance sensor). For example, a reduced cardiac stroke component of a transthoracic impedance signal correlates to an increase in heart size. In another example, the subject, caregiver, or another user enters an indication of the subject's heart size, based on an echocardiogram or other imaging measurement, into external user interface 110 of CHF parameter input device 145. An increase in heart size conelates to a future worsening of the subject's CHF status during the predetermined future time period.
In another example, the subject's intravascular blood pressure is used as a CHF physiologic parameter 200J. In one example, the subject's intravascular blood pressure is measured by implantable sensor 140 (e.g., a vena cava or right atrial pressure transducer). In another example, the subject, caregiver, or another user enters an indication of the subject's intravascular blood pressure (e.g., based on an external measurement) into external user interface 110 of CHF parameter input device 145. An increase in intravascular blood pressure correlates to a future worsening of the subject's CHF status during the predetermined future time period. i another example, the subject's dyspnea on exertion is used as a CHF physiologic parameter 200K. In one example, the rapid shallow breathing associated with dyspnea is measured by implantable sensors 140 including a respiration sensor (e.g., an impedance sensor) and an activity sensor (e.g., an accelerometer) to detect exertion. For example, an increase in respiratory rate together with an increase in activity, if accompanied by a decrease in tidal volume of the respiration, is indicative of dyspnea on exertion, hi another example, the subject, caregiver, or another user enters an indication of the subject's dyspnea on exertion into external user interface 110 of CHF parameter input device 145. An increase in dyspnea on exertion correlates to a future worsening of the subject's CHF status during the future predetermined time period. i another example, the subject's night cough (or cough while lying down) is used as a CHF physiologic parameter 20OL. In one example, the night cough is measured by an implantable sensor(s) 14O (e.g., a transthoracic impedance sensor) to detect the cough and a clock, a sleep detector, or a posture detector to respectively detect a time period during the night, the subject's sleep, and/or the subject's lying down. In another example, the subject, caregiver, or another user enters an indication of the subject's night cough into external user interface 110 of CHF parameter input device 145. An increase in night cough (or cough while lying down) correlates to a future worsening of the subject's CHF status during the future predetermined time period. i another example, the subject's heart rate is used as a CHF physiologic parameter 200M. In one example, heart rate is measured using an implantable sensor 140 (e.g., a cardiac signal sense amplifier coupled to an electrode 117A and/or 117B). In another example, the subject, caregiver, or another user enters an indication of the subject's heart rate (e.g., based on an external measurement) into external user interface 110 of CHF parameter input device 145. An increase in heart rate (e.g., average resting heart rate) coreelates to a future worsening of the subject's CHF status during the future predetermined time period.
In another example, the subject's pleural effusion (i.e., fluid in the subject's chest, but outside the subject's lungs) is used as a CHF physiologic parameter 200N. hi one example, pleural effusion is measured by an implantable sensor 140 that senses transthoracic impedance, a low frequency component of which changes with pleural effusion status. In another example, pleural effusion is measured on an X-ray or other image by a user, and an indication of the degree of pleural effusion is input to CHF parameter input device 145 by the user at external user interface 110. An increase in pleural effusion correlates to a future worsening of the subject's CHF status during the predetermined future time period.
In another example, the subject's peripheral edema (i.e., fluid retention in the extremities) is used as a CHF physiologic parameter 20OP. hi one example, a user, physician, or caregiver measures a swollen arm or leg (e.g., using a tape measure) and inputs an indication of the degree of peripheral edema to CHF parameter input device 145 at external user interface 110. An increase in peripheral edema conelates to a future worsening of the subject's CHF status during the predetermined future time period. hi another example, the subject's left ventricular end diastolic pressure
(LVEDP) is used as CHF physiologic parameter 200Q. In one example, LVEDP is measured using an implantable pressure sensor 140 disposed within in the subject's left ventricle. An increase in LVEDP correlates to a future worsening of the subject's CHF status during the predetermined future time period. hi another example, the subject's left atrial pressure ("LA pressure") is used as CHF physiologic parameter 200R. hi one example, LA pressure is 5 measured using an implantable pressure sensor 140 disposed within in the subject's left atrium. An increase in LA pressure correlates to a future worsening of the subject's CHF status during the predetermined future time period.
In another example, the subject's brain natriaetic peptide (BNP) level is used as CHF physiologic parameter 200S. BNP is released by the subject's body 0 in response to left ventricular stress. An increase in BNP correlates to a future worsening of" the subject's CHF status during the predetermined future time period. In one example, the subject's BNP level is measured by an external blood test, and an indication of the BNP level is input to CHF parameter input device 145 by the user at external user interface 110. In another example, the 5 subject's BNP level is measured by an implantable sensor 140 or an external (e.g., transdermal) sensor 135.
In a further example, therapy control module 155 adjusts a therapy being provided by pulse generator 160 to heart 120 based on at least one of the binary indication predicting whether a significant change in CHF status is expected to O occur within a predetermined future time period or on the multivalued underlying probability of the change in CHF status, hi one example, such therapy adjustment includes changing which electrodes are being used to deliver cardiac resynchromzation therapy for spatially coordinating heart contractions. In another example, such therapy adjustment includes initiating or 5 adjusting paired pacing. Paired pacing involves delivering a premature electrical energy pulse to a portion of the heart during a ti e period that excites heart tissue, but does not cause a corresponding heart contraction. The energy thus delivered increases an intracellular calcium concentration, and is followed by delivery of a second energy pulse during an immediately subsequent time period O that does trigger a resulting heart contraction. Thus, in this example, pacing a particular heart chamber of a subject at 75 beats per minute includes delivering pairs of pacing pulses at the 75 beats per minute rate, the first pacing pulse in the pair increasing intracellular calcium concentration, but not triggering a resulting heart chamber contraction, and the second pacing pulse in the pair using the increased calcium concentration in triggering a resulting heart chamber contraction. In an alternative example, the probability computation 205 takes the form of a conditional probability computation, such as described in Sweeney et al. U.S. Patent No. 6,272,377, which is assigned to Cardiac Pacemakers, Inc., and which is incorporated by reference herein in its entirety, including its description of using conditional probabilities to predict the likelihood of occurrence of a future event. In the present context, the future event is a CHF status change, and the CHF physiologic parameters serve as triggers/markers or, more generally, conditioning events. The weights correlating each CHF physiologic parameter to a future CHF status change are conditional probabilities that may alternatively be expressed as rates, as described in the above-incorporated Sweeney et al. reference.
One such example includes detecting a conditioning event (e.g., one of CHF physiologic parameters 200A-S) statistically associated with the occurrence of a CHF status change in a subject. In this example, device 105 predicts the occurrence of a CHF status change within a specified prediction time period if an estimated CHF status change probability exceeds a specified threshold value. The estimated CHF status change probability is computed from a conditional CHF status change probability, associated with the conditioning event, that is derived from past observations of instances in which the conditioning event occurs alone or together with a CHF status change within a specified time period. hi a further example, the conditional CHF status change probability CP is a ratio of the number of observed instances in which the conditioning event is followed by a CHF status change within a specified basic time period to the total number of observed instances of the conditioning event. In a further example, this involves estimating a rate C at which the conditioning event occurs. The estimated CHF status change probability is then calculated by the expression: estimated CHF status change probability =CP x ( 1- e"cτ), where T is a measure of the specified prediction time period. In one example, the conditional CHF status change probability is calculated by the expression:
CP=1- e RT, where T is a measure of the specified prediction time period, and R is an estimate of the rate at which the CHF status changes occur while the conditioning event is present. In a further example, a plurality of conditioning events statistically associated with the occunence of a CHF status change are detected, and a composite estimated CHF status change probability is compared with a threshold value in order to predict the occurrence of a CHF status change. The composite CHF status change probability is associated with a combination of the estimated CHF status change probabilities associated with each detected conditioning event, such as described in the above-incorporated Sweeney et al. reference.
It is to be understood that the above description is intended to be illustrative, and not restrictive. For example, the above-discussed examples may be used in combination with each other. Many other embodiments will be apparent to those of skill in the art upon reviewing the above description. The scope of the invention should, therefore, be determined with reference to the appended claims, along with the full scope of equivalents to which such claims are entitled. Moreover, the terms "first," "second," "third," etc. are used merely as labels, and are not intended to impose numeric requirements on their objects.
WHAT LS CLAuVTED IS:
1. A cardiac rhythm management system comprising: an implantable cardiac rhythm management device comprising: at least one congestive heart failure (CHF) physiologic parameter input device to provide CHF physiologic information about a subject; a processor circuit, comprising at least one processor input coupled to the at least one CHF physiologic parameter input device to receive a plurality of different CHF physiologic parameters, the processor comprising: weighting factors, stored in a memory, the weighting factors corresponding to each of the received CHF physiologic parameters; and a CHF status change probability indicator, to predict a likelihood of a subsequent change in a CHF status of a subject using the plurality of different received CHF physiologic parameters and the corresponding weighting factors.
2. The system of claim 1, in which a first weighting parameter, conesponding to a first received CHF physiologic parameter used to predict the likelihood of a subsequent change in the CHF status of the subject, is dependent on which at least one other received CHF physiologic parameter is also used to predict the likelihood of a subsequent change in CHF status.
3. The system of claim 1, in which a first weighting parameter, corresponding to a first received CHF physiologic parameter used to predict the likelihood of a subsequent change in the CHF status of the subject, is dependent on how many other received CHF physiologic parameters are also used to predict the likelihood of a subsequent change in CHF status.
4. The system of claim 1, in which the CHF status change probability indicator predicts a likelihood of a subsequent change in a CHF status of a subject by comparing to a threshold value a probability computed using the plurality of different received CHF physiologic parameters and the corresponding weighting factors.
9. The system of claim 1, further comprising an external remote user interface communicatively couplable to the implantable cardiac rhythm management device.
12. The system of claim 11 , in which the user interface is configured to receive from the user at least one CHF physiologic parameter comprising information about the subject's weight to communicate to the at least one CHF physiologic parameter input device in the implantable cardiac rhythm management device.
30. The system of claim 1, in which the at least one congestive heart failure (CHF) physiologic parameter input device includes at least one congestive heart failure (CHF) conditioning event input device to provide a CHF conditioning event statistically associated with the occunence of a CHF status change in a subject.
31. The system of claim 1, in which the processor circuit comprises at least one processor input coupled to the at least one CHF conditioning event input device to receive the CHF conditioning event, the processor comprising an indicator predicting the occurrence of a CHF status change within a specified prediction time period if an estimated CHF status change probability exceeds a specified threshold value, wherein the estimated CHF status change probability is computed from a conditional CHF status change probability, associated with the conditioning event, that is derived from past observations of instances in which the conditioning event occurs alone or together with a CHF status change within a specified time period.
33. The system of claim 31, further comprising an estimated rate C at which the conditioning event occurs, and further wherein the estimated CHF status change probability is calculated by the expression: estimated CHF status change probability =CP x ( 1- E"cτ).
CP=1- eRT, wherein T is a measure of the specified prediction time period, and R is an estimate of the rate at which CHF status changes occur while the conditioning event is present.
PCT/US2003/024597 1999-10-01 2003-08-06 Systems predicting congestive heart failure WO2004012815A1 (en)
US10/213,268 2002-08-06
JP2004526055A JP4602764B2 (en) 2002-08-06 2003-08-06 System to predict congestive heart failure
WO2004012815A1 true WO2004012815A1 (en) 2004-02-12
PCT/US2003/024597 WO2004012815A1 (en) 1999-10-01 2003-08-06 Systems predicting congestive heart failure
WO2013021383A1 (en) 2011-08-08 2013-02-14 Isonea (Israel) Ltd. Event sequencing using acoustic respiratory markers and methods
SG159387A1 (en) 2002-11-26 2010-03-30 Biocon Ltd In Modified natriuretic compounds, conjugates, and uses thereof
EP1680020B1 (en) * 2003-10-14 2015-06-17 Cardiac Pacemakers, Inc. Detection of congestion from monitoring patient response to a recumbent position
DE602005024179D1 (en) 2004-11-24 2010-11-25 Remon Medical Technologies Ltd An implantable medical device with integrated acoustic transducers
EP2244785A1 (en) 2008-01-22 2010-11-03 Cardiac Pacemakers, Inc. Respiration as a trigger for therapy optimization
AU2009293198B2 (en) * 2008-09-19 2013-07-04 Cardiac Pacemakers, Inc. Indication-based worsening HF alert
JP5465250B2 (en) * 2008-09-22 2014-04-09 カーディアック ペースメイカーズ， インコーポレイテッド Detection of decompensated congestive heart failure
US8738119B2 (en) * 2008-10-10 2014-05-27 Cardiac Pacemakers, Inc. Multi-sensor strategy for heart failure patient management
WO2014189885A1 (en) 2013-05-20 2014-11-27 Cardiac Pacemakers, Inc. Apparatus for heart failure risk stratification
CN105451648A (en) 2013-08-05 2016-03-30 心脏起搏器股份公司 System and method for detecting worsening of heart failure based on rapid shallow breathing index
EP3065625A1 (en) * 2013-11-04 2016-09-14 Cardiac Pacemakers, Inc. Heart failure detection and risk stratification system
DE59300252D1 (en) * 1993-08-13 1995-07-13 Siemens Ag A process for high-resolution spectral analysis for multichannel observations.
FR2780290B1 (en) 1998-06-26 2000-09-22 Ela Medical Sa Slave device active implantable medical such as pacemaker, defibrillator and / or cardioverter, including multi-type
US7127290B2 (en) 2006-10-24
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