1. Field of the Invention
The present invention generally relates to the field of implantable heart stimulation devices, such as pacemakers, implantable cardioverter-defibrillators (ICD), and similar cardiac stimulation devices that also are capable of monitoring and detecting electrical activities and events within the heart. More specifically, the present invention relates to a device for monitoring the heart cycle of a human heart such that coronary flow may be maintained at a desired level, a cardiac stimulator comprising such a device, and a method of monitoring the heart cycle of a human heart.
2. Description of the Prior Art
Implantable heart stimulators that provide stimulation pulses to selected locations in the heart, e.g. selected chambers, have been developed for the treatment of cardiac diseases and dysfunctions. Heart stimulators have also been developed that affect the manner and degree to which the heart chambers contract during a cardiac cycle in order to promote the efficient pumping of blood. The heart will pump more effectively when a coordinated contraction of both atria and both ventricles can be provided. In a healthy heart, the coordinated contraction is provided through conduction pathways in both the atria and the ventricles that enable a very rapid conduction of electrical signals to contractile tissue throughout the myocardium to effectuate the atrial and ventricular contractions. If these conduction pathways do not function properly, a slight or severe delay in the propagation of electrical pulses may arise, causing asynchronous contraction of the ventricles which would greatly diminish the pumping efficiency of the heart. Patients who exhibit pathology of these conduction pathways, such as patients with bundle branch blocks, etc., can thus suffer compromised pumping performance.
Various art procedures have been developed for addressing these and other disorders. For instance, cardiac resynchronization therapy (CRT) can be used for effectuating synchronous atrial and/or ventricular contractions. Furthermore, cardiac stimulators may be provided that deliver stimulation pulses at several locations in the heart simultaneously, such as biventricular stimulators. The stimulation pulses could also be delivered to different locations with a selected delay in an attempt to optimize the hemodynamic performance, e.g. maximize cardiac output, in relation to the specific cardiac dysfunction present at the time of implant. During follow-up, a physician may alter the delay settings in adaptation to altered cardiac status. However, none of the prior art procedures addresses the issue of maintaining the coronary flow for providing oxygen-rich blood to the myocardium at a desired level.
An object of the present invention is to address the problem of maintaining coronary flow at a desired level.
According to one aspect of the present invention, this object is achieved by a device for monitoring the heart cycle of a human heart such that coronary flow may be maintained at a desired level, the device being connectable to a first sensor adapted to be positioned at a first location of the heart and arranged for sensing cardiac wall movements at said first location, and to a second sensor adapted to be positioned at a second location of the heart and arranged for sensing cardiac wall movements at said second location. The device has processing circuitry configured to receive output signals from said first and second sensors, the output signals being indicative of myocardial relaxation at said first and second locations, to determine the time of myocardial relaxation at said first and second locations, and to provide a diastolic synchronization signal indicative of the synchrony or synchronicity in the time of myocardial relaxation between the first location and the second location.
According to another aspect of the present invention, the above object is achieved by an implantable cardiac stimulator for delivering stimulation pulses to a human heart. The cardiac stimulator has a housing, a pulse generator enclosed in the housing for generating the stimulation pulses, control circuitry for controlling the delivery of the stimulation pulses to the heart, and a device for monitoring the heart cycle of a human heart as described above. The stimulator is connectable to a lead arrangement for conducting said stimulation pulses to the heart and sensed electrical signals from the heart to the control circuitry. It is to be noted that the term “implantable cardiac stimulator” is intended to encompass any implantable device arranged for providing electrical stimuli for controlling the operation of a human heart, such as an ICD or a pacemaker, e.g. of biventricular, dual-chamber, AV-sequential, or any other type known in the art.
Thus, the present invention is based on the advantageous idea of monitoring the heart cycle for determining the synchronization of myocardial relaxation during the diastolic phase of the heart cycle. Thereby, conditions that are necessary for maintaining coronary flow at a desired level can be monitored, which enables the detection of the demand for suitable corrective action when the conditions change or deteriorate.
All coronary blood supply, or cardiac perfusion, occurs during the diastolic phase of the heart cycle, i.e. when the myocardium relaxes between contractions. At the onset of the systolic phase, the myocardial tissue is contracted, thereby also contracting the coronary arteries and arterioles such that coronary flow virtually comes to a stop during systole. When the myocardial tissue relaxes and dilates, the arteries and arterioles also become dilated and the pressure gradient built up during the systolic phase forces the flow of blood through the coronary arteries and veins. Thus, the diastolic phase should be sufficiently long for providing sufficient time for coronary flow to occur.
It has been found that disturbances in the diastolic phase may have an adverse effect on the cardiac perfusion, i.e. such that the coronary flow is decreased. Thereby, the myocardium may not get the amount of oxygen that is required for a sufficient or desired cardiac performance, resulting in an ischemic situation. Such disturbances can be due to asynchronous systole, and post-systolic contractions (PSC). All of these may result in localized contractions of the myocardium during the diastolic phase, which will disturb the coronary flow locally and may also disturb or prevent a simultaneous onset of the diastolic phase.
As stated above, in cardiac stimulation therapy, the stimulator settings should be adapted such that a synchronous diastole with an adequately long duration is achieved. Thus, the aim at the time of implant would be to localize a region with the occurrence of possible PSC that would disturb the synchronous onset or duration of diastole, and then to stimulate the heart using a stimulation therapy pattern such that the occurrences of PSC is removed or decreased. This can be performed by adjusting the timing parameters for the delivery of the stimulation pulses.
However, even though ventricular and atrial diastolic synchrony may be present at the time of implant, possibly supported by suitable cardiac stimulation therapy, this may not necessarily be the case at a later stage. For instance, during progression of cardiac therapy after implantation of a cardiac stimulator, the cardiac tissue may adapt itself to the new conditions. Then, the function of hibernating myocardial tissue may be at least partially restored, and the overall cardiac function may become different from that at the time of implant.
In other words, diastolic synchrony from the time of implant may turn into diastolic asynchrony at a later stage, possibly supported or induced by stimulation therapy, as a result of a local improvement in the local function of myocardial tissue. For instance, the functions of myocardial portions or regions that at the time of implant were affected by slow conduction or post-systolic contractions (PSC), could at a later stage have improved their behavior such that there is no longer any slow conduction or PSC, or the PSC patterns have changed. Thus, even though there is an improvement in the behavior of myocardial tissue through the remodulation or recovery of the heart during progression of cardiac therapy, a new cardiac situation has arisen by this improvement and an improvement of the changed overall function of the heart may be desired for adaptation to the new situation.
According to the invention, the heart cycle is monitored by sensing the heart wall movements during the heart cycle at a plurality of locations. The heart wall movements are sensed using at least two sensors that are attached to the heart wall and provide output signals indicative of the heart wall movements, in order for distinguishing between contractions and relaxations of the muscular heart wall tissue, i.e. the myocardium. The output signals from each sensor are provided through cardiac leads to processing circuitry provided in an implantable heart stimulator and used for determining onset and cessation of myocardial relaxation at the location of the sensor.
The processing circuitry receives the output signals provided by the respective sensors and determines any differences in time of myocardial relaxation for the myocardial tissue at the respective sensor location. If there are no differences, an indication of diastolic synchrony may be provided, which means that a satisfactory coronary flow is enabled.
The term “time of myocardial relaxation” may refer to the point in time of onset of myocardial relaxation, which indicates the onset of the diastolic phase. If there is a time difference between the onsets of myocardial relaxation at one sensor as compared to at the other sensor(s), the coronary flow may be greatly impaired during the time of asynchrony, i.e. when a portion of the myocardium is relaxed and another portion is contracted. Thereby, the time available between ventricular systole for supplying oxygen to the myocardial tissue is compromised, possibly resulting in impaired cardiac performance.
Furthermore, the term “time of myocardial relaxation” may additionally or alternatively refer to the time duration of myocardial relaxation, i.e. the portion of the diastolic phase that is not interrupted by any myocardial contraction, such as a regular systolic contraction or a PSC. Thus, not only the onset of myocardial relaxation is determined, but also the time duration during which the myocardium is in the relaxed state. Thereby, the time duration of simultaneous relaxation, i.e. diastole, for the myocardial locations at which the sensors are positioned may be determined, which indicates the time duration when the blood may flow through and oxygenate the myocardium. Thus, this time duration should be as large as possible for enabling optimal oxygenation of the myocardium during the heart cycle.
Since it is the diastolic phase that is of interest for the calculation of the synchronization index, an intracardiac electrogram, IEGM, could be used for providing an indication related to when the output signals of the sensors may be used for determining onset and end of the diastolic phase. Then, the processing circuitry could be arranged to only receive sensor output signals provided during the diastolic phase. Thereby, there will be no risk of misinterpreting an asynchrony that may be present in the systolic phase as an asynchrony in the diastolic phase.
Moreover, the processing circuitry calculates a synchronization signal or index, related to the diastolic phase, on the basis of the output signals from the respective sensors. These calculations could be performed in a number of different ways, as understood by those skilled in the art. For instance, the synchronization index or signal could be the actual difference time for the sensed onset of myocardial relaxation between the different sensors. In another example, the index could be related to the duration of simultaneous myocardial relaxation, for instance as a percentage of a measured or calculated optimal time duration.
In a further example, the difference between the sensor output signals could be calculated, for the diastolic phase, for instance by simply subtracting one output signal from another. The resulting difference signal could then be used as said synchronization signal per se, or statistical calculations could be applied to the difference signal to arrive at a suitable value indicative of the synchronization. If more than two sensors are used, a number of difference signals could be provided, for selected sensor combinations or for all combinations. The multiple difference signals could then simply be aggregated to obtain a synchronization signal that would take into account all sensors, or be subject to suitable statistical calculations to arrive at a synchronization index.
In yet further examples, the synchronization index or signal could be obtained through plotting of the sensor output signals in x-y plots and detecting patterns between the plots, for instance by cross-correlation, neural network signal processing, or loop discrimination. Such loop discrimination is disclosed in U.S. Pat. Nos. 5,427,112 and 5,556,419, which are incorporate herein by reference.
However, the present invention is not restricted to the examples of methods for calculating a synchronization index or signal presented herein. On the contrary, any suitable method for calculating a synchronization signal or index from the output signals of the sensors is contemplated within the scope of the present invention.
According to embodiments of the present invention, the processing circuitry is arranged for comparing the obtained synchronization index or signal with a threshold value or signal. Then, the threshold value would be an indicator whether the diastolic synchronization lies within an acceptable range or not. In other words, as long as the synchronization index is within a selected range, as defined by one or more threshold values, a desired level of coronary flow is considered to be enabled. However, should the synchronization index fall outside the intended range, an indication of diastolic asynchrony, or insufficient diastolic synchrony, may be provided.
Such an indication could in exemplifying embodiments of the invention be used for triggering a change in the stimulation therapy for the patient. Such a change could for example refer to an adjustment in the VV-interval, e.g. for a biventricular heart stimulator; a change in the AV-interval, e.g. for a dual chamber or an AV-sequential heart stimulator; or combinations thereof. Thereby, the diastolic synchrony can be monitored during remodulation of the patient's heart, and the pacing therapy can be adjusted in adaptation to the remodulation such that the coronary flow may be maintained at a desired level.
The changes in the timing parameters of the stimulation pulse delivery can, according to exemplifying embodiments, be performed in order to avoid or eliminate an asynchrony in the onset of the myocardial relaxation, i.e. an onset of the diastolic phase. Thus, if it is determined that there is an undesired difference in the time of onset of myocardial relaxation between the sensed, different portions of the myocardium, i.e. the portions for which the sensors are sensitive for cardiac wall movements, then the timing parameters of the stimulation pulse delivery may be amended such that a synchronized onset of myocardial relaxation is provided.
Furthermore, according to further exemplifying embodiments, changes in the timing parameters of the stimulation pulse delivery can be performed in order to reduce or avoid the occurrences of post-systolic contractions, PSC, which generally are localized events. As mentioned above, the occurrences of PSC during the diastolic phase, whether localized or involving the entire myocardium, will undoubtedly have a detrimental effect on the coronary flow locally. It may also disturb coronary flow that occurs in coronary arteries located downstream of those affected coronary arteries that are located in the myocardial region that contracts as a result of the PSC. Thus, by amending the timing parameters, suitably in a manner that has been previously determined to have an inhibiting effect on the occurrences of PSC, for instance at the time of implantation of the cardiac stimulator, the occurrences of undesired and detrimental PSC can be reduced and possibly even avoided.
Moreover, according to still further exemplifying embodiments, the changes in the timing parameters of the stimulation pulse delivery can be performed in order to lengthen the duration of simultaneous myocardial relaxation between the different portions of the myocardium for which cardiac wall movements are sensed. In other words, timing parameters are adjusted for obtaining as long time duration of simultaneous diastole as possible. Thereby, as long time as possible for enabling coronary flow to occur is provided. The detection and determination of simultaneous myocardial relaxation is interrupted if a PSC should occur within the diastolic phase. Thus, the term “simultaneous myocardial relaxation” refers to the time period from the onset of diastole for all sensed portions of the heart, until the onset of a myocardial contraction at any of the sensed portions of the heart, whether the contraction is a regular systolic contraction or an irregular post-systolic contraction.
As understood by those skilled in the art, the above described three objectives, i.e. simultaneous onset of myocardial relaxation, reduction or possible minimization of PSC, and extension or possible maximization of simultaneous duration of myocardial relaxation, is preferably combined when possible. Also, there may be situations when one must be prioritized over the other. Such prioritizing may be the subject of physician settings, or be pre-programmed shipping settings.
According to further embodiments of the invention, said three objectives can be adapted to the current heart rate, either intrinsic or stimulation induced stimulation. For example, it may be the aim for the changes in the timing parameters of the stimulation pulse delivery to achieve simultaneous onset at a basic heart rate, while at a higher heart rate the aim may be to extend the time duration of simultaneous myocardial relaxation, or vice versa.
Furthermore, according to still further exemplifying embodiments, if an asynchrony is detected at a high heart rate, the control circuitry of the cardiac stimulator may be arranged to reduce the heart rate. This may lead to a reduction of the cardiac output, but may on the other hand increase coronary flow since the time duration of diastole increases as a result of increased interval between cardiac contractions. Thus, for heart stimulators in which the pacing therapy may be automatically adjusted by the heart stimulator in order to optimize or maximize cardiac output, a synchronized and elongated diastolic phase may be given priority over the optimization of cardiac output. For instance, in patients suffering from ischemic heart disease, it may be more important to ensure synchronized diastole and, thereby, adequate coronary flow at all times rather than maximized cardiac output.
Suitable adjustments for avoiding or eliminating undesired diastolic asynchrony and restoring a suitable level of diastolic synchrony could according to exemplifying embodiments be determined or set prior to or during implantation of the cardiac stimulator. In such embodiments, sensor signals could be registered during a pre-set stimulation protocol, and synchronization index then be calculated for different pre-set stimulation conditions and settings. Examples of such pre-set stimulation protocols triggering changes in the timing parameters of stimulation pulse delivery could include an AV stimulation protocol with varying AV delays, a VV stimulation protocol with varying W delays, etc. During implantation, i.e. when the heart is studied with the sensors during no stimulation and various stimulation protocols, the expected changes in synchronization index at heart decompensation can be outlined. The term decompensation refers to a situation where changes in the demand for cardiac output of the patient, for instance when the patient rises from a sitting to a standing position or switches from walking to running, is not compensated for by the heart.
In further embodiments, the indication of diastolic asynchrony could be used for triggering an alarm signal to the patient. This alarm signal could be intended for prompting the patient to seek medical assistance for care or follow-up.
It should be understood that the indication of diastolic asynchrony does not have to be a binary value. On the contrary, the asynchrony indication preferably also provides information of the severity of asynchrony. Thus, the threshold value as referred to above, may in fact be a number of threshold values. For instance, a first value could be an indication of slight asynchrony to be used for diagnostic purposes, a second value could trigger a change in the pacing therapy, and a third value could be used for triggering an alarm to the patient that he needs to see his/her physician.
Furthermore, the change in timing parameters for the delivery of stimulation pulses may be performed in adaptation to the synchronization signal, or to the output signals from the wall movement sensors. Thus, the synchronization signal may provide an indication of the loss of synchrony, as well as further information which will provide information on how the lost synchrony is to be recovered. Furthermore, the sensor output signals may for instance provide information of the cause of the asynchrony. For instance, occurrences of diastolic asynchrony detected by two out of three sensors may provide an indication of where the source of the asynchrony occurred or originated. Moreover, the sensor output signals and/or the synchronization may suitably be stored for future use by the physician for diagnosis of occurred events at follow-up.
The monitoring of diastolic synchrony and/or detection of diastolic asynchrony is preferably performed at predetermined time intervals. As an example, the monitoring could be performed by receiving the output signals from the sensors, and providing a diastolic synchronization signal at any suitable predetermined or varied time interval given the current cardiac situation, e.g. once a week, every three days, once a day, every 8 hours, etc. Preferably, the time interval is set such that monitoring is performed often enough for an asynchrony to be detected at such an early stage that corrective action may be immediately taken and possible detrimental effects avoided, and seldom enough such that an unduly large energy consumption resulting from the monitoring procedure may be avoided.
In some embodiments, the time interval may be varied in adaptation to expected possible changes in the function of the heart. For instance, it may be expected that variations and changes in the myocardial function is most likely to occur, and to occur most frequently, in the time immediately following implantation. Thus, the monitoring interval can be set at a short interval for the period immediately following implant, and then be automatically extended as the time from implantation increases.
Furthermore, the time interval may be shortened as a result of detected changes in the diastolic synchrony. Thus, following a change in diastolic synchrony, possibly into asynchrony with ensuing corrective actions taking place, the time interval is suitably decreased in order to frequently monitor for possible further deterioration, or for an improvement as a result of the corrective actions taken.
Moreover, immediately following a change in the pacing therapy, determinations of possible asynchrony should take place. Also, if the synchronization signal or index is a quantitative value directly indicating the level of synchrony, the change in synchronization based on any pacing therapy variations can be monitored and the pacing therapy further adjusted accordingly.
In further examples, if the monitoring should indicate that diastolic asynchrony has arisen, then one or more further measurements and determinations of diastolic synchronization may be performed before an indication of diastolic asynchrony is provided and possible ensuing actions are initiated. Thereby, a sudden, isolated asynchronous event will not have an undue impact on the overall stimulation pacing therapy.
In exemplifying embodiments of the present invention, the synchronization monitoring is based on the output of two sensors, in which a first sensor is positioned at a location related to the right ventricle of the heart and arranged for sensing cardiac wall movements of the right ventricle, and the second sensor is positioned at a location related to the left ventricle of the heart and arranged for sensing cardiac wall movements of the left ventricle. Preferably, the right ventricle sensor is positioned within the right ventricle and attached to the ventricular wall, and the left ventricle sensor is positioned in the coronary sinus region outside the left ventricle and in contact with the left ventricular wall. In this example, interventricular diastolic synchronization is monitored. As used herein, the phrase “coronary sinus region” refers to the vasculature of the left ventricle, including any portion of the coronary sinus, great cardiac vein, left marginal vein, left lateral vein, left posterior ventricular vein, middle cardiac vein, and/or small cardiac vein or any other cardiac vein accessible via the coronary sinus.
In further exemplifying embodiments of the present invention, the synchronization monitoring is based on the output of two sensors positioned in or at the same ventricle. Then, the sensors are suitably used for monitoring intraventricular diastolic synchronization, for instance in the right ventricle. However, if one sensor is positioned within the right ventricle and attached to the cardiac septum, or in the immediate vicinity thereof, the sensor could be arranged to sense cardiac wall movements related to myocardial contraction and relaxation originating from the left ventricle.
Moreover, one or more additional sensors could in further examples of the invention be provided in or at the left or the right ventricle for providing additional output signal(s) on which the monitoring of diastolic synchronization is based. Also, sensors could be provided in the atrium for delivering output signal(s) on which the diastolic synchronization is based.
It should be noted that a number of different sensors could be used in the context of this invention for sensing cardiac wall movements, which are known per se to those skilled in the art. For example, the sensors could be in the form of accelerometers, of any suitable type, or in the form of piezoelectric pressure transducers. Thus, the scope of the present invention is not restricted to the particular sensor alternatives disclosed herein.
In the examples that will be presented in the following, the sensors are provided at the distal end of cardiac leads that are arranged for providing stimulation pulses to the atria and/or ventricles of the heart, or for conducting sensed intrinsic cardiac signals from the heart to the heart stimulator. However, it should be noted that sensors provided on separate implantable leads, or other implantable devices, are also contemplated in the context of this application. Thus, the scope of the present invention is not restricted to sensors arranged on such implantable leads for stimulation and sensing as will be discussed below.
Further objects and advantages of the present invention will be discussed below by means of exemplifying embodiments.
a-6c are schematic illustrations of the determination of diastolic synchrony according to embodiments of the present invention.
a-7c are schematic illustrations corresponding to those of
a-8c illustrate the determination of a diastolic asynchrony resulting from a local post-systolic contraction.
a-9d illustrate examples of sensor positions where all sensors are positioned at the left ventricle.
a-10d illustrate examples of sensor positions where sensors are positioned at both the right and the left ventricle, respectively.
a and 11b illustrate in diagram form a first example of how a synchronization index may be obtained.
a and 12b illustrate in diagram form a second example of how a synchronization index may be obtained.
The following is a description of exemplifying embodiments in accordance with the present invention. This description is not to be taken in a limiting sense, but is made merely for the purpose of describing the general principles of the invention. Thus, even though particular types of heart stimulators will be described, such as biventricular pacemakers with or without atrial sensing and/or stimulation, the invention is also applicable to other types of cardiac stimulators, such as univentricular or dual chamber pacemakers, implantable cardioverter defibrillators (ICD's), etc.
With reference first to
In order to sense right ventricular cardiac signals and to provide stimulation therapy to the right ventricle RV, the stimulation device 10 is coupled to an implantable right ventricular lead 20 having a ventricular tip electrode 22, a ventricular annular or ring electrode 24, and a cardiac wall movement sensor 21. The ring electrode 24 is arranged for sensing electrical activity, intrinsic or evoked, in the right ventricle RV. The right ventricular tip electrode 22 is arranged to be implanted in the endocardium of the right ventricle, e.g. near the apex 8 of the heart. Thereby, the tip electrode 22 becomes attached to the cardiac wall and follows the cardiac wall movements, which movements can be sensed by the sensor 21 arranged near the tip electrode. In this example, the sensor is fixedly mounted in a distal header portion of the lead 20, in which the tip electrode 22 is also fixedly mounted. Furthermore in this example, the sensor is in the form of an accelerometer. However, other arrangements sensor types are contemplated for the cardiac wall motion sensor 21.
In order to sense left ventricular cardiac signals and to provide pacing therapy for the left ventricle LV, the stimulation device 10 is coupled to a “coronary sinus” lead 30 designed for placement via the coronary sinus in veins located distally thereof, so as to place a distal electrode adjacent to the left ventricle. Also, additional electrode(s) (not shown) could be positioned adjacent to the left atrium. The coronary sinus lead 30 is designed to receive ventricular cardiac signals from the cardiac stimulator 10 and to deliver left ventricular LV pacing therapy using at least a left ventricular tip electrode 32 to the heart 1. In the illustrated example the LV lead 30 comprises an annular ring electrode 34 for sensing electrical activity related to the left ventricle LV of the heart. Furthermore, a cardiac wall movement sensor 31 is arranged at the tip electrode 32 for sensing left ventricular LV cardiac wall movements.
Turning briefly to
Furthermore,
Although three examples have been illustrated in
Turning now to
In corresponding manner, a second tip electrode 32 is positioned in a vein distally of the coronary sinus and, thus, connected to the left ventricle LV of the heart 1, and, via a conductor in the second lead 30, to a second pulse generator 36. A second ring electrode 34 is located near the second tip electrode 32 and connected, via a further conductor in the second electrode lead 30, to the second pulse generator 36. Delivery of a stimulation pulse to the ventricle can be bipolar via the second tip electrode 32 and the second ring electrode 34, or unipolar via the second tip electrode 32 and the indifferent electrode 12. A second detector 38 is connected in parallel across the output terminal of the second pulse generator 36 in order to sense left ventricular activity in the heart. The pulse generators 26 and 36 and the detectors 28 and 38 are controlled by a control unit 40 which regulates the stimulation pulses with respect to amplitude, duration and stimulation interval, the sensitivity of the detectors 28 and 38 etc.
A physician using an extracorporeal programmer 44 can, via a telemetry unit 42, communicate with the heart stimulator 10 and thereby obtain information on identified conditions and also reprogram the different functions of the heart stimulator 10.
The output signal from the measurement unit 52, which is proportional to the measurement signal, is then sent to a buffer 54 and to a differentiating circuit 56. Buffering is performed so that the differentiated signal is in phase with the proportional signal when they are sent to a calculator unit 58. The calculator unit 58 calculates a diastolic synchronization or synchrony value or signal based on the output signals from the respective sensors. The calculated synchronization signal is sent to a comparator 60 for comparison with a threshold value, for instance indicative of when insufficient diastolic synchrony is present.
The output signal from the comparator represents information as to whether the synchronization signal passes the threshold value, or one of the threshold values for embodiments where a plurality of threshold values are utilized, and is forwarded to a microprocessor 62 which communicates with the control unit 40. If, e.g., an arisen asynchrony is identified, the control device 40 can institute therapeutic treatment with stimulation pulses in order to restore diastolic synchrony. The microprocessor 62 further controls the measurement unit 52 with respect to the measurement signal to be sent to the analysis device 50 and can also control the comparator 60, for example for varying threshold values in response to altered pacing therapy or due to altered settings by the physician.
With reference now to
Furthermore, a fourth conductor 76 provides an IEGM signal for the measurement unit. The IEGM signal is used by the analysis device 50, or rather by the differentiating circuit 54 and the calculator unit 58, as an aid in discriminating between the systolic and the diastolic phases of the heart cycle. The analysis device 50 can be configured to process only sensor output signals provided during the diastolic phase. Thus, there will be no risk of misinterpreting an asynchrony that may be present in the systolic phase as an asynchrony in the diastolic phase.
c and 7a-7c show in schematic form the presence and determination of diastolic synchrony and asynchrony, respectively. In
In
In
Turning now to
In
Turning to
In
Turning now to
In
In the example illustrated in
When the signal output from the sensors a, b and c is received by the analysis device 50, a calculation of a synchronization index or signal is performed, which can be used for determining synchrony of the heart. In
The resulting difference signals are shown in
a and 12b illustrate a further example of deriving one or more synchronization indices or signals. Here, the upper and lower portions of the diagram in
When the monitoring of diastolic synchronization has revealed that a diastolic asynchrony has arisen, or that a reduction of diastolic synchrony has occurred, the parameters for timing of stimulation pulse delivery may be changed in order to restore or improve the diastolic synchrony. Such a change could for example refer to an adjustment in the W-interval, e.g. for a biventricular heart stimulator; a change in the AV-interval, e.g. for a dual chamber or an AV-sequential heart stimulator; or combinations thereof. Thereby, the diastolic synchrony can be monitored and the pacing therapy adjusted such that the coronary flow may be maintained at a desired level.
In further embodiments, the indication of diastolic asynchrony could be used for triggering an alarm signal to the patient. This alarm signal could be intended for prompting the patient to seek medical assistance for care or follow-up.
It should be noted that the sensors may be subjected to pressures, movements and/or accelerations that are not derived from or related to the intrinsic movements of the myocardium and the cardiac walls thereof. For instance, accelerations derived from extra-cardiac movements of the patient, such as from running, vibrations in the patient environment, thoracic movements etc. However, output signal contributions deriving from intrinsic movements of the myocardial tissue can easily be discriminated from signal contributions from such extra-cardiac movements since the latter have a substantially identical impact on the respective sensor. Furthermore, by designing the sensors to be sensitive for certain frequency ranges, the majority of the extra-cardiac signal contributions may be omitted. Furthermore, band-pass filtering of the sensor outputs may also be used for discriminating or filter out the signal contribution from extra-cardiac movements.
Although modifications and changes may be suggested by those skilled in the art, it is the intention of the inventor to embody within the patent warranted heron all changes and modifications as reasonably and properly come within the scope of her contribution to the art.
Filing Document | Filing Date | Country | Kind | 371c Date |
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PCT/SE05/01808 | 11/30/2005 | WO | 00 | 5/15/2008 |