Apparatus for detecting a depolarization wave of the heart and atrial defibrillator utilizing same

Abstract: An atrial defibrillator (30) reliably detects a depolarization activation wave of the heart and delivers cardioverting electrical energy to the atria of the heart in synchronism with a detected depolarization activation wave. The atrial defibrillator includes a first sensor (53,52) for producing a first electrical output having a duration substantially equal to the duration of the depolarization activation wave sensed between a first pair of spaced apart locations (38a,40a) of the heart. The atrial defibrillator further includes a second sensor for producing a second electrical output having a duration substantially equal to the duration of the depolarization activation wave sensed between a second pair of spaced apart locations of the heart. The spacing between the second pair of locations is greater than the spacing between the first pair of locations. A microprocessor (60) is responsive to the first and second electrical outputs for providing an indication signal indicating the occurrence of the depolarization activation wave when the second electrical output is longer in duration than the first electrical output. A pulse generator (66) coupled to the microprocessor applies electrical cardioverting energy to the atria of the heart in response to the indication signal.

Description: The present invention generally relates to an apparatus for detecting a depolarization activation wave (R wave) of the heart. The present invention is more particularly directed to an atrial defibrillator for delivering cardioverting electrical energy to the atria of the heart in synchronism with the detected depolarization activation wave. Implantable atrial defibrillators have been proposed to provide patients suffering from occurrences of atrial fibrillation with relief. Synchronizing the delivery of the defibrillating or cardioverting electrical energy with a depolarization activation wave (R wave) of the heart is important to prevent ventricular fibrillation. Ventricular fibrillation is a fatal arrhythmia which can be caused by electrical energy being delivered to the heart at the wrong time in the cardiac cycle, such as during the T wave of the cycle. As a result, it is most desirable to sense depolarization activation waves of the heart to generate synchronization pulses (or signals) in a manner which avoids detecting noise as a depolarization activation wave. WO-A-92/18198 - a publication falling under Art. 54(4) EPC - discloses an implantable atrial defibrillator providing pulse of defibrillating electrical energy to the atria of the heart in synchronism with sensed R waves in response to non-coincident sensing of an R wave at first and second areas of the heart. The defibrillating pulse is provided after a predetermined number of consecutive R waves are non-coincidently sensed to assure reliable synchronization. The object of the invention is to provide an apparatus for the reliable detection of depolarization activation waves of the heart which can be used for the delivery of electrical cardioverting energy to the atria of the heart in synchronism with a detected depolarization activation wave. According to the invention this object is achieved by the apparatus of claim 1. Advantageous embodiments of the invention are described in the dependent claims. Briefly, the present invention provides an apparatus for reliably detecting a depolarization activation wave of the heart. The apparatus includes first sensing means in electrical contact with the heart between a first pair of spaced apart locations for producing a first electrocardiogram of the heart and first output means coupled to the first sensing means and responsive to the first electrocardiogram for isolating a predetermined feature of the first electrocardiogram and producing a first output characteristic of the feature of the first electrocardiogram. The apparatus further includes second sensing means in electrical contact with the heart between a second pair of spaced apart locations for producing a second electrocardiogram of the heart, and second output means coupled to the second sensing means and responsive to the second electrocardiogram for isolating the predetermined feature of the second electrocardiogram and producing a second output characteristic of the feature of the second electrocardiogram. The apparatus further includes discriminating means coupled to the first and second output means and responsive to said first and second electrical outputs for discriminating between the predetermined features of the first and second electrocardiograms and for indicating the occurrence of the depolarization activation wave when the predetermined features of said first and second electrocardiograms are different. In the apparatus of the present invention the spacing between the first pair of locations is different than the spacing between the second pair of locations, the first and second electrical outputs have durations substantially equal to the durations of the depolarization activation wave sensed by the first and second sensors respectively, and the predetermined characteristic is the duration of the first and second electrical outputs respectively. BRIEF DESCRIPTION OF THE DRAWINGS Figure 1 is a schematic block diagram of a fully implantable atrial defibrillator embodying the present invention in accordance with a first preferred embodiment thereof and shown in association with a human heart in need of atrial fibrillation monitoring and potential cardioversion of the atria. Figure 2 is a series of waveforms illustrating representative electrocardiograms of a cardiac cycle of the heart including a depolarization activation wave sensed between first and second pairs of locations of the heart illustrated in Figure 1 and first and second generated electrical outputs having durations substantially equal to the durations of the depolarization activation wave of the electrocardiogram as sensed between the first and second pairs of locations of the heart. Figure 3 is a schematic block diagram similar to Figure 1 illustrating a second preferred embodiment of the present invention. Figure 4 is a schematic block diagram similar to Figure 1 illustrating a third preferred embodiment of the present invention. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Referring now to Figure 1, it illustrates a fully implantable atrial defibrillator 30 embodying the present invention shown in association with a schematically illustrated human heart 10 in need of atrial fibrillation monitoring and potential cardioversion of the atria. The portions of the heart 10 illustrated in Figure 1 are the right ventricle 12, the left ventricle 14, the right atrium 16, the left atrium 18, the superior vena cava 20, the coronary sinus 22, the coronary sinus ostium or opening 24, the left ventricular free wall 26, and the inferior vena cava 28. In addition, as used herein, the term "depolarization activation waves" denotes R waves of the heart cardiac cycle which induce depolarizations of the ventricles 12 and 14. The atrial defibrillator 30 generally includes an enclosure 32 for hermetically sealing the internal circuit elements of the atrial defibrillator, an endocardial first lead 34, and an intravascular second lead 36. The enclosure 32 and first and second leads 34 and 36 are arranged to be implanted beneath the skin of a patient so as to render the atrial defibrillator 30 fully implantable. The endocardial first lead 34 preferably comprises an endocardial bi-polar lead having electrodes 38 and 40 arranged for establishing electrical contact with the right ventricle 12 of the heart 10. The electrodes 38 and 40 permit bi-polar sensing of depolarization activation waves in the right ventricle between a first pair of locations 38a and 40a within the right ventricle 12. As illustrated. the lead 34 is fed through the inferior vena cava 28, into the right atrium 16, and then into the right ventricle 12. As will be appreciated by those skilled in the art, a second path for lead 34 could alternatively be through the superior vena cava 20, into the right atrium 16, and then into the right ventricle 12. The second lead 36 generally includes a first or distal electrode 42, a second or ring electrode 44, and a third electrode 46. As illustrated, the second lead 36 is flexible and arranged to be passed down the superior vena cava 20, into the right atrium 16, into the coronary sinus ostium 24, and advanced into the coronary sinus 22 of the heart near the left side thereof so that the first or distal electrode 42 is within the coronary sinus or within a coronary vein, such as the great vein of the heart (not shown) adjacent the left ventricle 14. The electrodes 42, 44, and 46 are spaced apart such that when the first electrode 42 is within the coronary sinus 22 or a coronary vein adjacent the left ventricle 14, the second electrode 44 is beneath the left atrium 18 near the left ventricle 14 and the third electrode 46 is within either the right atrium 16 or the superior vena cava 20 and preferably within the right atrium 16. The first electrode 42 of the second lead 36 and the electrode 38 of the first lead 34 permit bi-polar sensing of depolarization activation waves between a second pair of locations 38a and 42a of the heart. Alternatively, the second pair of electrodes may include electrodes 42 and 40 and, as a result, the second pair of locations may be locations 42a and 40a. As will be noted in Figure 1, the spacing between the second pair of locations 38a and 42a is greater than the spacing between the first pair of locations 38a and 40a. As will be seen hereinafter, these relative spacings between the first and second pairs of locations between which depolarization activation waves are sensed enable reliable detection of depolarization activation waves in accordance with the present invention. The second electrode 44 together with the third electrode 46 of the second lead 36 provide for the delivery of defibrillating or cardioverting electrical energy to the atria. Because the second electrode 44 is located beneath the left atrium 18 near the left ventricle 14 and the third electrode 46 is within either the right atrium 16 or the superior vena cava 20 and above the coronary sinus ostium 24, the electrical energy applied between these electrodes will be substantially confined to the atria 16 and 18 of the heart 10. As a result, the electrical energy applied to the right ventricle 12 and left ventricle 14 when the atria are cardioverted or defibrillated will be minimized. Within the enclosure 32, the atrial defibrillator 30 includes a first sense amplifier 50, a first R wave detector 52, a second sense amplifier 54, a second R wave detector 56 and a third sense amplifier 58. Within the enclosure 32, the atrial defibrillator 30 also includes a microprocessor 60 and a pulse generator 66. As also can be seen in Figure 1, the microprocessor 60 includes a first timer 62 and a second timer 64. The first sense amplifier 50 includes a first input 68 which is coupled to electrode 38 of the first lead 34 and a second input 70 which is coupled to electrode 40 of the first lead 34. The first sense amplifier 50 thus senses the electrical activity of the heart 10 between the first pair of locations of the heart 38a and 40a. It amplifies the sensed electrical activity of the heart and provides at an output 72 an amplified signal or first electrocardiogram representative of the electrical activity of the heart sensed by the bi-polar electrodes 38 and 40. The first R wave detector 52 includes an input 74 which is coupled to the output 72 of the first amplifier 50. The R wave detector 52 includes a threshold detecting means or circuit which provides a substantially constant first electrical output having a duration substantially equal to the duration of the depolarization activation waves (R waves) sensed between electrodes 38 and 40. As a result, the electrodes 38 and 40 and the first sense amplifier 50 form a first sensing means 53 for sensing electrical activity of the heart including depolarization activation waves between the first pair of spaced apart locations of the heart 38a and 40a. The first R wave detector 52 forms a first output means for isolating the R wave feature of the first electrocardiogram and for producing a first electrical output, at output 76, having a first duration corresponding and substantially equal to the duration of the depolarization activation waves (R waves) sensed between the first pair or locations of the heart 38a and 40a. The second sense amplifier 54 includes a first input 78 which is coupled to the electrode 42 of the second lead 36 and a second input 80 which is coupled to electrode 38 of the first lead 34. As a result, the second sense amplifier 54 senses the electrical activity of the heart between the second pair of locations of the heart 38a and 42a. It provides at an output 82 an amplified signal or second electrocardiogram representative of the electrical activity of the heart sensed between the second pair of locations of the heart 38a and 42a. The second R wave detector 56 includes an input 84 for receiving the amplified signal provided from the output 82 of the second sense amplifier 54. The second R wave detector 56 also includes a second threshold detecting means or circuit for providing a substantially constant second electrical output at output 86 having a duration substantially equal to the duration of the depolarization activation waves sensed by the second sense amplifier 54. As a result, electrode 42, electrode 38, and sense amplifier 54 form a second sensing means 57 for sensing electrical activity of the heart including depolarization activation waves between the second pair of locations of the heart 38a and 42a. The second R wave detector 56 forms a second output means for isolating the R wave feature of the second electrocardiogram for producing a second electrical output having a second duration corresponding and substantially equal to the duration of the depolarization activation waves (R waves) sensed between the second pair of locations of the heart 38a and 42a. When the heart 10 is in need of cardioversion or defibrillation, the first timer 62 times the duration of the first electrical output provided by the first R wave detector 52 for timing the duration of a depolarization activation wave (R wave) sensed between the first pair of locations 38a and 40a. The second timer 64 also times the duration of the second electrical output provided by the second R wave detector 56 for timing the duration of the same depolarization activation wave (R wave) sensed between the second pair of locations 42a and 38a. Since the spacing between the second pair of locations 42a and 38a is greater than the spacing between the first pair of locations 40a and 38a, if the electrical activity of the heart sensed by the first sensing means 53 and second sensing means 57 is a true depolarization activation wave (R wave), the duration of the second electrical output provided by R wave detector 56 will be longer than the duration of the first electrical output provided by the first R wave detector 52. Hence, the predetermined features (R waves) of the first and second electrocardiograms and more specifically, the first and second predetermined characteristics (durations) of those features will be different. If the second electrical output is longer in duration than the first electrical output, the microprocessor 60 immediately provides an indication signal on line 65 indicating that a depolarization activation wave (R wave) has been detected. Thus, the microprocessor 60 forms a discriminating means which is responsive to the first and second electrical outputs for providing an indication signal indicating the occurrence of the depolarization activation wave. The microprocessor 60 discriminates between a depolarization activation wave and noise responsive to the second electrical output having a duration which is longer than the duration of the first electrical output. If the electrical activity of the heart sensed by the first and second sensing means 53 and 57 respectively is noise, a characteristic of the first and second electrical outputs, such as duration, will be substantially the same. As a result, when noise is detected, the microprocessor 60 will not provide the indication signal over line 65. The pulse generator 66 is of the type well known in the art which includes a storage capacitor for storing an electrical charge. Upon receiving the indication signal from the microprocessor 60 over line 65, the pulse generator 66 delivers electrical cardioverting energy to the atria of the heart. To that end, the pulse generator 66 includes a first output 90 which is coupled to electrode 46 of the second lead 36 and a second output 92 which is coupled to electrode 44 of the second lead 36. As a result, the electrodes 44 and 46 of the second lead 36 apply the electrical cardioverting energy provided by the pulse generator 66 to the atria 16 and 18 of the heart 10. To determine when cardioversion or defibrillation of the atria of the heart 10 is required, the third sense amplifier 58 senses electrical activity in the atria 16 and 18 of the heart 10. To that end, the third sense amplifier 58 includes a first input 98 which is coupled to electrode 46 and a second input 100 which is coupled to electrode 44. The third sense amplifier 58 includes an output 102 which is coupled to the microprocessor 60 for providing the microprocessor 60 with an amplified signal representing the electrical activity of the atria 16 and 18 of the heart. The microprocessor 60 digitizes the amplified electrical signal provided by the third sense amplifier 58 and processes the digitized values of the atrial activity for detecting atrial fibrillation. Such atrial fibrillation detection may be implemented by the microprocessor 60. Alternatively, the microprocessor 60 may be implemented in accordance with the atrial fibrillation detection algorithms disclosed in a paper: Janice Jenkins, Ki Hong Noh, Alain Guezennec, Thomas Bump, and Robert Arzbaecher, "Diagnosis of Atrial Fibrillation Using Electrograms from Chronic Leads: Evaluation of Computer Algorithms," PACE , Vol. 11, pp. 622-631, May 1988. Implementing such algorithms by a microprocessor such as microprocessor 60 is well within the purview of one skilled in the art. Referring now to Figure 2, it illustrates a first amplified electrocardiogram signal 72a provided by the first sense amplifier 50, a first electrical output 76a provided by the first R wave detector 52, a second amplified electrocardiogram signal 82a provided by the second sense amplifier 54, and a second electrical output 86a provided by the second R wave detector 56. All of the foregoing waveforms are generated responsive to the detection of the same electrical activity of the heart including a depolarization activation wave (R wave). As will be noted from Figure 2, when the first amplified signal 72a exceeds a voltage threshold (V t ) established by R wave detector 52, the R wave feature of the first electrocardiogram is isolated and the R wave detector 52 provides the first electrical output 76a having a duration of T 1 . Similarly, when the second amplified signal 82a provided by sense amplifier 54 exceeds a threshold voltage (V t ) established by R wave detector 56, the R wave feature of the second electrocardiogram is isolated and the R wave detector 56 provides the second electrical output 86a having a duration of T 2 . As can be appreciated by those skilled in the art, the R wave detectors 52 and 56 should have a relatively slow response to changes in input voltage amplitude to render the electrical outputs substantially constant in amplitude notwithstanding zero crossings of the amplified electrical signals as is evident by amplified electrical signal 82a. As will be noted in Figure 2, the duration (T 2 ) of the second electrical output 86a is longer than the duration (T 1 ) of the first electrical output 76a. Given such inputs to the microprocessor 60, the microprocessor determines that the R wave features of the first and second electrocardiograms are different because T 2 is greater than T 1 and hence determines that a legitimate depolarization activation wave (R wave) has been detected. Immediately following such a determination, the microprocessor 60 provides the indication signal on line 65 indicating that a legitimate depolarization activation wave has been detected. Referring now to Figure 3, it illustrates a second preferred embodiment of the present invention. As will be noted in Figure 3, the configuration of the atrial defibrillator 30 within enclosure 32 is the same as that illustrated in Figure 1. As a result, like reference numerals to indicate identical elements are carried throughout Figure 3. It will be noted from Figure 3, however, that sensing electrode 42, instead of being incorporated within the second lead 36, is now incorporated within the first lead 34. As a result, all three electrodes 38, 40, and 42 for sensing electrical activity including depolarization activation waves of the heart 10 are carried on a single lead, lead 34, and are all disposed for electrical contact with the heart within the right ventricle 12. Inputs 68 and 70 of sense amplifier 50 are still coupled to electrodes 38 and 40 respectively of the first lead 34. As a result, the first sense amplifier 50 senses electrical activity of the heart 10 between electrodes 38 and 40 and hence between the first pair of locations of the heart 38a and 40a. Input 80 of second sense amplifier 54 is still coupled to electrode 38 of lead 34, but now, input 78 of second sense amplifier 54 is coupled to electrode 42 which is now carried by the first lead 34. As a result, the second sense amplifier 54 senses electrical activity of the heart between electrodes 38 and 42 and hence between the second locations of the heart 38a and 42a. As will be noted from the Figure, since electrode 42 is of greater distance from electrode 38 than is electrode 40, the spacing between the second pair of locations 38a and 42a is greater than the spacing between the first pair of locations 38a and 40a. As a result, when a depolarization activation wave (R wave) is sensed by sense amplifiers 50 and 54, waveforms similar to that shown in Figure 2 will result. Hence, the overall operation of the atrial defibrillator 30 as shown in Figure 3 is the same as the overall operation of the atrial defibrillator as illustrated in Figure 1. The electrical cardioverting energy is still applied to the atria 16 and 18 between electrodes 44 and 46 and atrial activity of the heart is also sensed between electrodes 44 and 46. Referring now to Figure 4, it illustrates a third preferred embodiment of the present invention. Again, the configuration of the atrial defibrillator 30 within enclosure 32 is essentially identical to the configuration of the atrial defibrillator as illustrated in Figure 1 and therefore, again, like reference numerals indicating like elements are carried throughout Figure 4. While in the first and second embodiments of Figures 1 and 3 respectively the first and second pairs of locations between which electrical activity of the heart is sensed are defined by the locations of three electrodes, with the location of one electrode being in common to both pairs of locations, the first and second pairs of locations between which electrical activity of the heart is sensed in Figure 4 are defined by the locations of four electrodes. To that end, it will be noted that inputs 68 and 70 of the first sense amplifier 50 are still coupled to electrodes 38 and 40 for sensing electrical activity of the heart between locations 38a and 40a. However, input 78 of second sense amplifier 54 is coupled to electrode 42 of the second lead 36 and input 80 of second sense amplifier 54 is now coupled to electrode 44 of the second lead 36. As a result, the second sense amplifier 54 senses heart activity between a second pair of locations of the heart 42a and 44a. In addition, the second lead 36 is fed further down the coronary sinus 22 such that the spacing between electrodes 42 and 44 is greater than the spacing between electrodes 38 and 40. As a result, the spacing between the second pair of locations 42a and 44a is greater than the spacing between the first pair of locations 38a and 40a. Also, and as a result, the first pair of locations 38a and 40a are still in the right ventricle while the second pair of locations 42a and 44a are in the left ventricle. In all other respects, the operation of the atrial defibrillator 30 may remain the same as previously described. Electrodes 46 and 44 may still be utilized for applying cardioverting or defibrillating electrical energy to the atria 16 and 18 of the heart 10 and electrodes 44 and 46 may still be utilized for detecting atrial activity of the heart for detecting atrial fibrillation. While particular embodiments of the present invention have been shown and described, modifications may be made. For example, unipolar sensing may be employed for establishing the first or second pair of sensing location. More specifically, in the embodiment of Figure 1, the second pair of sensing locations may be established between electrode 38 and the enclosure of the atrial defibrillator 30. Furthermore, any electrocardiogram feature may be isolated for discrimination purposes. For example, the Q wave feature of the electrocardiogram or the Q wave to R wave relation may be isolated and utilized for discrimination. Therefore it is intended in the appended claims to cover all such changes and modifications which fall within the scope of the claims.

Claims: An apparatus for reliably detecting a depolarization activation wave of the heart - an R-wave -, the apparatus including a first sensor (53) adapted for electrical contact with the heart between a first pair of spaced apart locations (38a, 40a) for sensing the depolarization activation wave, a second sensor (57) adapted for electrical contact with the heart between a second pair of spaced apart locations (38a, 42a; 42a, 44a) for sensing the depolarization activation wave, a first output circuit (52) coupled to the first sensor (53) for producing a first electrical output representative of the duration of the depolarization activation wave as sensed by the first sensor; a second output circuit (56) coupled to the second sensor (57) for producing a second electrical output representative of the duration of the depolarization activation wave as sensed by the second sensor; and a discriminator (60) coupled to the first and second output circuits (52, 56) for discriminating between the first and second electrical outputs and for providing an indication of the occurrence of the depolarization activation wave when the durations of the depolarization activation waves at the first and second electrical outputs, resp., are different; the spacing between the first pair of locations (38a, 40a) being different than the spacing between the second pair of locations (38a, 42a; 42a, 44a), the first and second electrical outputs having durations substantially equal to the durations of the depolarization activation wave sensed by the first and second sensors (53, 57) respectively. An apparatus as defined in claim 1 further characterized in that the spacing between the second pair of locations (38a, 42a; 42a, 44a) is greater than the spacing between the first pair of locations (38a, 40a) and wherein the - discriminator (60) indicates the occurrence of the depolarization activation wave when the second electrical output is longer in duration than the first electrical output. An apparatus as defined in claim 1 further characterized in that the first sensor (53) includes first and second electrodes (38, 40) adapted for electrical contact with the heart for sensing the depolarization activation wave between the first pair of locations (38a, 40a) and the second sensor (57) includes either the first or second electrode (38 or 40) and a third electrode (42) adapted for electrical contact with the heart for sensing the depolarization activation wave between the second pair of locations (38a, 42a; 42a, 44a). An apparatus as defined in claim 3 further characterized in that a first lead (34) includes the first and second electrodes (38, 40) and a second lead (36) includes the third electrode (42). An apparatus as defined in claim 4 further characterized in that the first and second electrodes (38, 40) are adapted for electrical contact with the right ventricle of the heart and the third electrode (42) is adapted for electrical contact with the left ventricle of the heart. An apparatus as defined in claim 3 further characterized in that a single lead (34) includes the first, second, and third electrodes (38, 40, 42). An apparatus as defined in claim 6 further characterized in that the first, second, and third electrodes (38, 40, 42) are adapted for electrical contact with the right ventricle of the heart. An apparatus as defined in claim 1 further characterized in that the first sensor (53) includes first and second electrodes (38, 40) adapted for electrical contact with the heart for sensing the depolarization activation wave between the first pair of locations (38a, 40a) and the second sensor (57) includes third and fourth electrodes (42, 44) adapted for electrical contact with the heart for sensing the depolarization activation wave between the second pair of locations (38a, 42a; 42a, 44a). An apparatus as defined in any preceding claims further characterized in that the apparatus forms a part of an atrial defibrillator (30) which delivers cardioverting electrical energy to the atria of the heart in synchronism with the detected depolarization activation wave and includes a pulse generator (66) coupled to the discriminator (60) and is responsive to the indication for applying electrical cardioverting energy to the atria of the heart.

Inventors: ADAMS JOHN M, ALFERNESS CLIFTON A, INFINGER KENNETH ROSS, ADAMS, JOHN M., ALFERNESS, CLIFTON A., INFINGER, KENNETH ROSS
Applicants: CARDIAC PACEMAKERS INC, CARDIAC PACEMAKERS, INC.
Application year: 1993
Main classification: A61N1
IPC codes: A61N1