Abstract:
Currently, brady, tachy and CRT devices all provide stored electrograms that record ambulatory electrograms with programmable trigger mechanisms. The present invention comprises an implantable device with additional capability that can store polysomnograms and phonocardiograms. The polysomnograms can be obtained from an impendent sensor of the type used in minute ventilation-based rate-adaptive pacemakers. The phonocardiograms are obtained from an accelerometer transducer or other type sensors that can detect heart sound.

Description:
BACKGROUND OF THE INVENTION 
     1. Field of the Invention 
     This invention relates generally to body-implantable, medical apparatus, and more particularly to a cardiac rhythm management device (CRMD) having a capability of recording polysomnogram (PSG) data and/or phonocardiogram (heart sound) data upon the detection of pre-programmed conditions or events. 
     2. Discussion of the Prior Art 
     State of the art implantable medical devices, such as pacemakers and defibrillators, typically embody a microprocessorbased controller capable of receiving as inputs, digitized signals corresponding to heart depolarization events and other sensor derived outputs and for controlling a pulse generator that generates tissue-stimulating pulses in accordance with a program stored in a memory for the microprocessor-based controller. Such devices also typically include a telemetry link whereby programmed data and operands can be exchanged between the implanted device and an external programmer/monitor. 
     The memory in the implant may also be used to record, when enabled, electrogram signals for later read-out and analysis by a medical professional. 
     It is also known that cardiac pacing can be used as a therapy for patients with congestive heart failure (CHF). Algorithms have been developed for establishing a AV-delay interval that optimizes the pumping performance of the sick heart. 
     In applying cardiac pacing as a treatment for CHF, not only is electrogram data derived from an implanted CRMD of interest, but other physiologic sensor derived data may also prove helpful in treating the patient. For example, heart sound data can prove meaningful. 
     As is well known, the first heart sound, S 1 , is initiated at the onset of ventricular systole and consists of a series of vibrations of mixed, unrelated, low frequencies. It is the loudest and longest of the heart sounds, has a decrescendo quality, and is heard best over the apical region of the heart. The tricuspid valve sounds are heard best in the fifth intercostal space, just to the left of the sternum, and the mitral sounds are heard best in the fifth intercostal space at the cardiac apex. 
     S 1  is chiefly caused by oscillation of blood in the ventricular chambers and vibration of the chamber walls. The vibrations are engendered by the abrupt rise of ventricular pressure with acceleration of blood back toward the atria, and the sudden tension and recoil of the A-V valves and adjacent structures with deceleration of the blood by the closed A-V valves. The vibrations of the ventricles and the contained blood are transmitted through surrounding tissue and reach the chest wall where they may be heard or recorded. 
     In accordance with the present invention, an implanted CRMD may include an accelerometer as a sound transducer and because implanted in close proximity to the heart, may develop a robust electrical signal that can be digitized and stored in the memory of the implant. 
     The intensity of the first sound is primarily a function of the force of the ventricular contraction, but also of the interval between atrial and ventricular systoles. If the A-V valve leaflets are not closed prior to ventricular systole, greater velocity is imparted to the blood moving toward the atria by the time the A-V valves are snapped shut by the rising ventricular pressure, and stronger vibrations result from this abrupt deceleration of the blood by the closed A-V valves. 
     The second heart sound, S 2 , which occurs on closure of the semi-lunar valves, is composed of higher frequency vibrations, is of shorter duration and lower intensity, and has a more “snapping” quality than the first heart sound. The second sound is caused by abrupt closure of the semi-lunar valves, which initiates oscillations of the columns of blood and the tensed vessel walls by the stretch and recoil of the closed valve. Conditions that bring about a more rapid closure of the semi-lunar valve, such as increases in pulmonary artery or aorta pressure (e.g., pulmonary or systemic hypertension), will increase the intensity of the second heart sound. In the adult, the aortic valve sound is usually louder than the pulmonic, but in cases of pulmonary hypertension, the reverse is often true. 
     The third heart sound, which is more frequently heard in children with thin chest walls or in patients with left ventricular failure due to CHF, consists of a few low intensity, low-frequency vibrations. It occurs in early diastole and is believed to be due to vibrations of the ventricular walls caused by abrupt acceleration and deceleration of blood entering the ventricles on opening of the atrial ventricular valves. 
     A fourth or atrial sound, (S 4 ), consisting of a few low-frequency oscillations, is occasionally heard in normal individuals. It is caused by oscillation of blood and cardiac chambers created by atrial contraction. 
     When S 3  and S 4  sounds are accentuated, it may be indicative of certain abnormal conditions and are of diagnostic significance. Therefore, the ability to store heart sound information for later playback can prove beneficial to medical professionals following patients in whom cardiac pacemakers and/or defibrillators are implanted. 
     In addition to heart sound information, benefit can also be derived from the storage and later read out from an implanted CRMD of respiratory related data. While external polysomnograph equipment can be worn for recording respiratory related data over extended time intervals, the ability to derive polysomnograms from an implanted CRMD can prove to be beneficial. Such things as Cheyne-Stokes respiration patterns, Biot&#39;s respiration, Epnustic breathing and central neurogenic hypoventilation and hyperventilation can be detected and recorded. 
     In Cheyne-Stokes respiration, respiratory rate and tidal volume gradually increase, then gradually decrease to complete apnea, which may last several seconds. Then, tidal volume and breathing frequency gradually increases again, repeating the cycle. This pattern occurs when cardiac output is low, as in CHF, delaying the blood transit time between the lungs and the brain. In this instance, changes in respiratory center Pco 2  lag changes in arterial Pco 2 . For example, when an increased Paco 2  from the lungs reaches the respiratory neurons, ventilation is stimulated, which then lowers the atrial Pco 2  level. By the time this reduced Paco 2  reaches the medulla to inhibit ventilation, hyperventilation has been in progress for an inappropriately long time. When blood from the lung finally does reach the medullary centers, the low Paco 2  greatly depresses ventilation to the point of apnea. Atrial Pco 2  then rises, but a rise in respiratory center Pco 2  is delayed because of low blood flow rate. The brain eventually does receive the high Paco 2  signal, and the cycle is repeated. Cheyne-Stokes respiration also may be caused by brain injuries, in which respiratory centers correspond to changes Pco 2  level are damaged. 
     It is accordingly a principal object of the present invention to provide an implantable CRMD capable of producing and storing in a memory phonocardiograms of heart sounds and polysomnograms reflecting respiratory events for later readout from the device via a conventional telemetry link used in such devices. 
     It is still another object of the present invention to establish certain triggering mechanisms for enabling the memory to capture certain respiratory patterns such as those related to Cheyne-Stokes patterns by monitoring tidal volume or respiratory rate variations with respect to a pre-determined threshold. Similarly, the system may be enabled to capture heart sound information when, for example, atrial fibrillation occurs or, perhaps, at a certain level of exercise. 
     SUMMARY OF THE INVENTION 
     The foregoing objects are achieved in accordance with the present invention by providing an implantable cardiac rhythm management device of a type having a microprocessor-based controller along with a memory. The CRMD may also comprise a pulse generator for producing cardiac stimulating pulses at times determined by the program run on the microprocessor-based controller. Alternatively, the implant may be a purely diagnostic device. The CRMD also incorporates a means for sensing at least one of respiratory related activity and heart sounds. A triggering device is incorporated that is responsive to a predetermined event for initiating storage of data pertaining to the sensed one of respiratory related activity and heart sounds in the memory. As an example, upon detection of a predetermined respiratory pattern, the memory may be enabled for storing polysomnogram data. Alternatively, the occurrence of an event, such as an onset of atrial fibrillation, may be used to trigger the memory so as to store phonocardiogram data. The recording function in the memory of the implanted device can also be manually triggered, using an external magnet. 
    
    
     DESCRIPTION OF THE DRAWINGS 
     The foregoing features, objects and advantages of the invention will become apparent to those skilled in the art from the following detailed description of a preferred embodiment, especially when considered in conjunction with accompanying drawings in which like numerals in the several views refer to corresponding parts. 
     FIG. 1 is a block diagram of an implantable CRMD incorporating circuitry for capturing phonocardiograms and polysomnograms for subsequent readout to an external monitor; 
     FIG. 2 represents a polysomnogram recording. 
     FIG. 3 is a software flow diagram of an algorithm for storing polysomnogram data; 
     FIGS. 4A through 4D, when arranged as in FIG. 4, is a plot of left atrial, aortic, and left ventricular pressure pulses correlated in time with aortic flow, ventricular volume, heart sounds, venus pulse, and electrocardiogram for a complete cardiac cycle; and 
     FIG. 5 is a software flow diagram of an algorithm for storing heart sound data. 
    
    
     DESCRIPTION OF THE PREFERRED EMBODIMENT 
     With reference to FIG. 1, an implantable cardiac rhythm management device (CRMD) is shown as being enclosed in a broken line box  10  and, for exemplary purposes only, is represented as a rate adaptive pacemaker in which minute ventilation is the rate controlling parameter. As mentioned above, the implanted device may be purely diagnostic in nature and need not have a tissue stimulating capability. 
     The device includes a microprocessor  12  having a ROM memory  14  adapted to store a program of instructions, a RAM memory  16  for storing operands and data and an I/O module  18  for controlling a telemetry circuit  20  whereby bi-directional communications can be established between the implanted module  10  and an external monitor  22  via telemetry link  24 . The implanted device  10  is connected to a cardiac site by conductors  26  in a pacing/sensing lead  28  having tissue contacting electrodes  30  and  32  thereon. Those skilled in the art will appreciate that one or more conductors  26  in the lead  28  may be eliminated with the remaining conductors shared between the sense and pace functions. Cardiac depolarization signals, e.g., R-Waves picked up by the electrodes  30  and  32 , are applied by way of a sense amplifier  34  to an input of the microprocessor  12 . Those skilled in the art can also appreciate that the implanted CRMD  10  may also include an atrial sense amplifier adapted to receive atrial depolarization signals (P-Waves) so that both P-Wave events and R-Wave events can be conveyed to the microprocessor  12 . 
     Operating under control of a program stored in the ROM  14 , the microprocessor  12  is shown in the exemplary embodiment as being connected in controlling relationship, via line  36 , to a pulse generator  38  which is adapted to deliver tissue stimulating pulses, via the lead  28 , to target tissue in the heart. 
     Being a rate adaptive pacemaker, means are provided for adjusting the rate at which the pulse generator  38  delivers its stimulating pulses to the lead  28 . In the embodiment of FIG. 1, minute ventilation (MV) is provided as the rate controlling parameter. As such, an oscillator  40  is provided for delivering sub-threshold RF pulses, typically at a frequency of about 30 KHz, between an electrode  42 , which may be located on the lead  28 , and an electrode  44 , which may be the metal can comprising the housing for the CRMD  10 . As is well known in the art, respiratory activity (inhalation and exhalation) modulates the 30 KHz carrier signal, which is fed through a sensing amplifier  46  to a demodulator circuit  48 . The demodulator functions to recover the modulating envelope. Changes over time in the trans-thoracic impedance caused by respiratory activity produces an analog signal on line  42  which is then fed through a signal processing circuit  44  and an analog to digital converter  46  before being applied as an input to the microprocessor  12 . Those skilled in the art will appreciate that the A/D converter  46  may itself be implemented in the microprocessor  12  and need not necessarily be a separate module as depicted in FIG.  1 . 
     In accordance with the present invention, there is also provided an accelerometer type transducer  48  within the CRMD  10  and its output is amplified at  50  and appropriately signal processed at  52  to remove DC baseline shift and signal energy due to body motion before being digitized by the A/D converter  46  and fed to the microprocessor  12 . 
     FIG. 2 illustrates diagrammatically a polysomnogram illustrating nasal/oral airflow evidencing apnea episodes. As mentioned above, Cheyne-Stokes respiration frequently appears in patients whose cardiac output is low due to CHF. 
     FIG. 3 is a simplified software flow diagram of an algorithm for triggering the capture (recording) of respiratory pattern information in the event that an abnormal pattern in terms of respiratory rate and/or tidal volume is sensed. At block  54  the microprocessor continues to scan the digitized output from the signal processing circuit  44  to determine whether the trans-thoracic impedance versus time output from the demodulator  48  matches a pre-determined pattern (Block  56 ). If a match is detected, the RAM memory  16  is enabled and the digitized polysomnogram information is stored therein (Block  58 ). The RAM continues to store the polysomnogram data until such time as the test at block  60  determines that a preprogrammed time interval sufficient to capture relevant respiratory data has elapsed. 
     Once the polysomnogram information is stored in the RAM, it can be later transferred, via I/O module  18  and the telemetry circuit  20 , to an external monitor  22  for print out or display to a medical professional. 
     Referring next to FIG. 4, the correlation between heart sounds and events in the cardiac cycle is displayed for a patient with a normal heart. Also shown in the diagram of FIG. 4 are plots of left atrial, aortic and left ventricular pressure pulses that are correlated time wise with aortic blood flow, variations in ventricular volume, venus pulse and an electrocardiogram for one cardiac cycle. 
     FIG. 5 is a software flow diagram for triggering the recording of phonocardiogram data in the random access memory  16  in the CRMD  10  upon the occurrence of a pre-determined event. As indicated at block  70 , the output from the accelerometer  48  is continually scanned by the microprocessor  12  and when a triggering event, such as the detection of atrial fibrillation (block  72 ), the RAM  16  is enabled to store the phonocardiogram data (blocks  74 ). The phonocardiogram data is recorded for a preprogrammed time interval, and when the programmed time interval times out (block  76 ) storage of the data in the memory terminates with control returning to the input of block  70 . 
     A physician may select to record heart sounds based on criteria other than an episode of atrial fibrillation. For example, the test at block  72  may be based upon the patient reaching a certain level of exercise as determined by measured heart rate. Any other meaningful criteria may also be used as the triggering event for storing the phonocardiogram data. 
     While the invention has been illustrated and described in detail in the drawings and foregoing description, the same is to be considered as illustrative and not restrictive in character, it being understood that only the preferred embodiment has been shown and described and that all changes and modifications that come within the spirit of the invention are desired to be protected. For example, the preferred embodiment cardiac rhythm management device has been described for use in a rate adaptive pacemaker, however, it may be used in a defibrillator, an antitachy pacer, a diagnostic-only device or in another type of implantable electronic device where it is desired to monitor polysomnograms and/or phonocardiogram data.