Source: https://patents.google.com/patent/US20040098055A1/en
Timestamp: 2019-01-18 13:00:34
Document Index: 463459080

Matched Legal Cases: ['art 28', 'art 28', 'art 28', 'art 28', 'art 28', 'art 28', 'art 28', 'art 77', 'art 122', 'art 122', 'art 122', 'art 122', 'art 122', 'art.\n10', 'art.\n16', 'art.\n28']

US20040098055A1 - Implantable device - Google Patents
US20040098055A1
US20040098055A1 US10468867 US46886703A US2004098055A1 US 20040098055 A1 US20040098055 A1 US 20040098055A1 US 10468867 US10468867 US 10468867 US 46886703 A US46886703 A US 46886703A US 2004098055 A1 US2004098055 A1 US 2004098055A1
US10468867
US7203550B2 (en )
An apparatus for treating an infection which may occur in the biofilm which surrounds an implanted cardiac stimulation device, e.g., a cardioverter-defibrillator)ICD) or pacemaker. Such inflections are relatively untreatable by conventional antibiotics treatments. Thus, explanting of the implanted devices may be required. Accordingly, the present apparatus provides an electrical treatment that enables a biocide, i.e., an antibiotic, to successfully treat the infection within the biofilm and thus avoid the necessity to explant the device. Furthermore, the present invention provides this electrical treatment in a manner to not interfere with the stimulation pulses of the cardio stimulation device by alternatively delivering current pulses during atrial and ventricular refractory periods or a high frequency square wave at a frequency that exceeds the frequency response of the heart muscle.
The present invention relates generally to an apparatus for killing microorganisms which may form in a biofilm on surfaces of implanted devices and, more particularly, to such an apparatus used with a cardiac stimulation device, e.g., a cardioverter-defibrillator (ICD), pacemaker or the like. [0001]
Infections which may occur with pacemaker/ICD devices are relatively untreatable without device removal since the bacteria live in a biofilm on the device which blocks antibiotics. When the biofilm of such an implantable device becomes infected, it is almost universally impossible to treat the infection with systemic antibiotics. The standard medical procedure is to explant the device, leading to additional costs, risks and discomfort to the patient. [0002]
The reason that device infections cannot be treated by systemic antibiotics is that the biofilm protects the bacteria from systemic antibiotics and allows them to tolerate levels of antibiotics that are several orders of magnitude above that which can safely be given to a patient. [0003]
To overcome this tolerance to antibiotics, the use of electrical fields to kill bacteria in the biofilm has been investigated and discussed in the prior art Exemplary patents include U.S. Pat. Nos. 5,312,813; 5,409,467; and 5,462,644. [0004]
The present Invention is directed to an apparatus for treating an infection which may occur in the biofilm which surrounds an implanted cardiac stimulation device, e.g., a cardioverter-defibrillator (ICD) or a pacemaker. Such infections are relatively untreatable by conventional antibiotics treatments. Thus, explanting of the implanted devices may be required. Accordingly, the present apparatus provides an electrical treatment that enables a biocide, i.e., an antibiotic, to successfully treat the infection within the biofilm and thus avoid the necessity to explant the device. Furthermore, the present invention provides this electrical treatment in a manner to not interfere with the stimulation pulses of the cardiac stimulation device. [0005]
A biofilm is a conglomerate of microbial organisms imbedded in a highly hydrated matrix of exopolymers, typical polysaccharides and other macromolecules. Unlike planktonic organisms which are relatively susceptible to antibiotics, the structural matrix established during biofilm formation can make the colonizing cells able to withstand normal treatment doses of a biocide. However, the application of a relatively low current on the order of perhaps 10-100 microamperes per square centimeter is sufficient to allow the antibiotics to penetrate the biofilm and destroy the bacteria. [0006]
In one study (ASAIO Journal 1991; 38:M174-M178, Prevention and Control of Bacterial Infections Associated with Medical Devices by Khoury et al), the curve presented in FIG. 1 was generated. The solid line shows only a minimal reduction in the concentration of living biofilm cells after a dozen hours of the application of an antibiotic. On the other hand, by applying a low current, the number of living biofilm cells dropped by one order of magnitude every two hours. [0007]
The present invention provides an electric current to treat an infection in the surrounding biofilm of an implanted cardiac stimulation device, e.g., a cardioverter-defibrillator (ICD), pacemaker or the like. More specifically, a first coil, i.e., the SVC coil, is implanted in the region of the right atrium and a second coil, i.e., the RV coil, or other suitable electrode is implanted in the right ventricle (RV). Currents are delivered between the RV coil and from the SVC coil to the conductive case of an implanted cardiac simulation device to treat the infection. [0008]
Currents on the order of 15 microamperes per square centimeter are considered therapeutic for this process. Due to the heterogeneities of the current in an ICD surface, for example, one must be conservative in estimating the currents. It is desirable to assume a very cautious position, that the current density in the device housing varies by 100:1 from the highest to the lowest current density. To simplify the calculations, it is further assumed that the lowest current density is {fraction (1/10)} of the average. Thus, an average-current density of 150 microamperes per square centimeter is needed to guarantee the minimum requirement for purposes of the invention. Assuming a device having a 70 cm[0009] 2 surface area, this results in a treatment level of about 10 ma for the average current to the device. This average current is preferably maintained for about 10 hours (see FIG. 1) to achieve a maximum therapeutic benefit. However, a 10 ma current from an implantable coil to the case of a cardiac stimulation device is also capable of pacing the heart and thus care must be taken to not induce an arrhythmia. Accordingly, the present invention supplies an infection control current in a manner to not interfere with either the natural pacing of the heart or pacing pulses supplied or sensed by an implanted cardiac stimulation device. Accordingly, the risk of causing an arrhythmia is minimized.
In a first embodiment, the application of the infection control current is restricted to the refractory periods of portions, e.g., the atria and/or ventricles, of the cardiac muscle (i.e., the heart). Since the heart cannot be stimulated during these time periods, the heart's operation is not affected by this infection control current In a next operational mode, the infection control current is applied at a frequency that is too high to stimulate the heart. [0010]
Thus, a primary feature, of the present invention is the use of electric currents to control/treat infections associated with a cardiac stimulation device without adversely effecting the operation of the cardiac stimulation device or the heart. [0011]
Another feature of the present invention is the use of the casing (housing) of the device as one of its electrodes for supplying (or sinking) the electrical current. [0012]
In a first treatment mode, the present invention is used, preferably in conjunction with a course of antibiotics, when an infection is first detected. [0013]
In a second treatment mode, the present invention can be used prophylactically following implantation of the cardiac stimulation device in conjunction with the traditionally applied antibiotic treatment that follows surgery. [0014]
Other and further features, advantages, and benefits of the invention will become apparent in the following description taken in conjunction with the following drawings. It is to be understood that the foregoing general description and the following detailed description are exemplary and explanatory but are not to be restrictive of the invention. The accompanying drawings which are incorporated in and constitute a part of this invention, illustrate one of the embodiments of the invention, and together with the description, serve to explain the principles of the invention in general terms. Like numerals refer to like parts throughout the disclosure.[0015]
FIG. 1 is a graph comparing the success of killing biofilm cells over time with antibiotics alone as compared with antibiotics within an electric field. [0016]
FIG. 2 shows a simplified functional block diagram of an implantable cardioverter-defibrillator (ICD), which represents one type of implantable stimulation device with which the present invention may be used. [0017]
FIG. 3 shows a functional block diagram of an implantable dual-chamber pacemaker, which represents another type of implantable stimulation device with which the invention may be used. [0018]
FIG. 4 is a diagrammatic illustration of an implanted cardiac stimulation device in combination with a pectoral implant embodying the invention including one electrode in the region of the right atrium and another electrode in the right ventricle. [0019]
FIG. 5 is an electrogram with indications, according to the invention, of electrical currents from the electrode in the region of the atrium and from the electrode in the ventricle wherein the electrical infection control currents are supplied during refractory periods. [0020]
FIG. 6 illustrates a high-speed square wave generated from the electrodes to the housing of the cardiac stimulation device and the resulting response by the heart cells wherein the square wave is supplied at a frequency that is too high to significantly stimulate the heart.[0021]
The present invention is directed to an apparatus for treating an infection which may occur in the biofilm which surrounds an implanted cardiac stimulation device, e.g., a cardioverter-defibrillator (ICD) or a pacemaker. Such infections are relatively untreatable by conventional antibiotics treatments. Thus, explanting of the implanted devices may be required. Accordingly, the present apparatus provides an electrical treatment that enables a biocide, i.e., an antibiotic, to successfully treat the infection within the biofilm and thus avoid the necessity to explant the device. Furthermore, the present invention provides this electrical treatment in a manner to not interfere with the stimulation pulses of the cardiac stimulation device. [0022]
As indicated above, the present invention may be used with various types of implantable stimulation devices, including an implantable pacemaker configured to treat bradycardia and/or tachycardia, an implantable cardioverter-defibrillator (ICD), or a combination thereof. Such devices controvmonitor the operations of a patient's heart. [0023]
To better understand the invention, it will first be helpful to have an understanding of the basic functions performed by exemplary implantable stimulation devices with which the invention may be used, e.g., an ICD with dual chamber coils and/for a dual-chamber pacemaker. While a dual-chamber device has been chosen for this description, this is for teaching purposes only. It is recognized that the present invention could be implemented into a single-chamber device, that one of skill in the art could readily adapt the dual-chamber device shown in FIG. 3 to perform single-chamber functionality, and that a single-chamber device is within the spirit of the invention. [0024]
In FIG. 2, there is shown a simplified functional block diagram of an ICD device [0025] 20, and in FIG. 3, there is shown a simplified functional block diagram of a dual-chamber pacemaker 70. It should also be noted that in some instances the functions of an ICD and a pacemaker may be combined within the same cardiac stimulation device. However, for teaching purposes, the devices will be described as separate cardiac stimulation devices.
It is the primary function of an ICD device to sense the occurrence of an arrhythmia, and to automatically apply an appropriate electrical shock therapy to the heart aimed at terminating the arrhythmia. To this end, the ICD device [0026] 20, as shown in the functional block diagram of FIG. 2, includes a control and timing circuit 22, such as a microprocessor, state-machine or other such control circuitry, that controls a high output charge generator 26. The high output charge generator 26 generates electrical stimulation pulses of moderate or high energy (corresponding to cardioversion or defibrilation pulses, respectively), e.g., electrical pulses having energies of from 1 to 10 joules (moderate) or 11 to 40 joules (high), as controlled by the control/timing circuit 22.
Such moderate or high energy pulses are applied to the patient's heart [0027] 28 through at least one lead 30 having at least two defibrillation electrodes, such as coil electrodes 38 and 40. The lead 30 preferably also includes at least one electrode for pacing and sensing functions, such as electrode 32. Typically, the lead 30 is transvenously inserted into the heart so as to place the coil electrodes 38 and 40 in the apex of the heart and in the superior vena cava, respectively. While only one lead is shown in FIG. 2, it is to be understood that additional defibrillation leads and electrodes may be used as desired or needed in order to efficiently and effectively apply the shock treatment generated by the high voltage generator 26 to the patient's heart 28.
The ICD [0028] 20 also includes a sense amplifier 42 that is coupled to at least one sensing electrode 32. It is the function of the sense amplifier 42 to sense the electrical activity of the heart 28, as is known in the art, such as R-waves which occur upon the depolarization, and hence contraction, of ventricular tissue; and P-waves which occur upon the depolarization, and hence contraction, of atrial tissue. Thus, by sensing R-waves and/or P-waves through the sense amplifier 42, the control/timing circuit 22 is able to make a determination as to the rate and regularity of the patient's heart beat Such information, in turn, allows the control/timing circuit 22 to determine whether the heart 28 of a patient is experiencing an arrhythmia, and to apply appropriate stimulation therapy. Alternatively, a pacing pulse generator 43 can be used to periodically drive electrode 42 to maintain heart operation.
The control/timing circuit [0029] 22 further has a memory circuit 44 coupled thereto wherein the operating parameters used by the control/timing circuit 22 are stored. Such operating parameters define, for example, the amplitude of each shock energy pulse to be delivered to the patient's heart 28 within each tier of therapy, as well as the duration of these shock pulses. The memory 44 may take many forms, and may be subdivided into as many different memory blocks or sections (addresses) as needed to store desired data and control information. A feature of an exemplary ICD 20 is the ability to sense and store a relatively large amount of data as a data record, which data record may then be used to guide the operation of the device, i.e., the present operating mode of the device may be dependent, at least in part, on past performance data.
Advantageously, the operating parameters of the implantable device may be non-invasively programmed into the memory [0030] 44 through a telemetry circuit 46, in telecommunicative contact with an external programmer 48 by way of a suitable coupling coil 50. The coupling coil 50 may serve as an antenna for establishing a radio frequency (RF) communication link 52 with the external programmer 48, or the coil 50 may serve as a means for inductively coupling data to and from the telemetry circuit 46 from and to the external programmer 48, as is known in the art. See, e.g., U.S. Pat. Nos. 4,809,697 (Causey, III et al.) and 4,944,299 (Silvian), incorporated herein by reference. Further, such telemetry circuit 46 advantageously allows status information relating to the operation of the ICD 20, as contained in the control/timing circuit 22 or memory 44, to be sent to the external programmer 48 through the established link 52.
The control/timing circuit [0031] 22 includes appropriate processing and logic circuits for analyzing the output of the sense amplifier 42 and determining if such signals indicate the presence of an arrhythmia. Typically, the control/timing circuit 22 is based on a microprocessor, or similar processing circuit, which includes the ability to process or monitor input signals (data) in a prescribed manner, e.g., as controlled by program code stored in a designated area or block of the memory 44. The details of the design and operation of the control/timing circuit 22 are not critical to the present invention. Rather, any suitable control/timing circuit 22 may be used that performs the functions described herein. The use, design, and operation of microprocessor-based control circuits to perform timing and data analysis functions is known in the art.
The ICD [0032] 20 additionally includes a battery 62 which provides operating power to all of the circuits of the ICD 20.
In FIG. 3, a simplified block diagram of the circuitry needed for a dual chamber pacemaker [0033] 70 is illustrated. The pacemaker 70 is coupled to a heart 28 by way of leads 74 and 76, the lead 74 having an electrode 75 that is in contact with one of the atria of the heart, and the lead 76 having an electrode 77 that is in contact with one of the ventricles of the heart. The leads 74 and 76 are electrically and physically connected to the pacemaker 70 through a connector 73 that forms an integral part of the housing wherein the circuits of the pacemaker are housed. Typically, leads 74 and 76 are operated in a bipolar mode where a “tip” portion provides the voltage signal that provides current that flows to a “ring” portion on the same lead. Alternatively, leads 74 and 76 can operate in a unipolar mode where current flows from the “tip” portion of each lead to a conductive case 128 which surrounds the pacemaker device 70.
The connector [0034] 73 is electrically connected to a protection network 79, which network 79 electrically protects the circuits within the pacemaker 70 from excessive shocks or voltages that could appear on the electrodes 75 and/or 77 in the event such electrodes were to come in contact with a high voltage signal, e.g., from a defibrillation shock.
The leads [0035] 74 and 76 carry stimulation pulses to the electrodes 75 and 77 from an atrial pulse generator (A-PG) 78 and a ventricular pulse generator (V-PG) 80, respectively. Further, electrical signals from the atria are carried from the electrode 75, through the lead 74, to the input terminal of an atrial channel sense amplifier (P-AMP) 82; and electrical signals from the ventricles are carried from the electrode 77, through the lead 76, to the input terminal of a ventricular channel sense amplifier (R-AMP) 84. Similarly, electrical signals from both the atria and ventricles are applied to the inputs of an intracardiac electrogram amplifier (IEGM) 85. The amplifier 85 is typically configured to detect an evoked response from the heart 28, i.e., a response to an applied simulation pulse, thereby aiding in the detection of “capture”. (Capture occurs when an electrical stimulus applied to the heart is of sufficient energy to depolarize the cardiac tissue, thereby causing the heart muscle to contract, or in other words, causing the heart to beat. Capture does not occur when an electrical stimulus applied to the heart is of insufficient energy to depolarize the cardiac tissue.) Following each captured stimulation pulse, the associated cardiac tissue (i.e., the atria or the ventricles) enters into a refractory period when it cannot be restimulated.
The dual-chamber pacemaker [0036] 70 is controlled by a control system 86 that typically includes a microprocessor programmed to carry out control and timing functions. The control system 86 receives the output signals from the atrial (P-AMP) amplifier 82 over signal line 88. Similarly, the control system 86 receives the output signals from the ventricular (R-AMP) amplifier 84 over signal line 90, and the output signals from the IEGM amplifier 85 over signal line 91. These output signals are generated each time that an intrinsic P-wave or an R-wave or an evoked response is sensed within the heart 28. As with each evoked response, the cardiac tissue enters into a refractory period following each intrinsic P-wave or R-wave during which time period the associated cardiac tissue, i.e., the atria or the ventricles, cannot be restimulated. The control system 86 also generates trigger signals that are sent to the atrial pulse generator (A-PG) 78 and the ventricular pulse generator (V-PG) 80 over signal lines 92 and 94, respectively, to control the amplitude and duration of the signals delivered to the electrodes, 73 and 77. These trigger signals are generated each time that a stimulation pulse is to be generated by the respective pulse generator 78 or 80. The atrial trigger signal is referred to simply as the “A-trigger”, and the ventricular trigger signal is referred to as the “V-trigger”.
During the time that either an A-pulse or V-pulse is being delivered to the heart, the corresponding amplifier, P-AMP [0037] 82 and/or RAMP 84, is typically disabled by way of a blanking signal presented to these amplifiers from the control system over signal lines 96 and 98, respectively. This blanking action prevents the amplifiers 82 and 84 from becoming saturated from the relatively large stimulation pulses that are present at their input terminals during this time. This blanking action also helps prevent residual electrical signals present in the muscle tissue as a result of the pacemaker stimulation from being interpreted as P-waves or R-waves.
As shown in FIG. 3, the pacemaker [0038] 70 further includes a memory circuit 100 that is coupled to the control system 86 over a suitable data/address bus 102. This memory circuit 100 allows certain control parameters, used by the control system 86 in controlling the operation of the pacemaker, to be programmably stored and modified, as required, in order to customize the pacemaker's operation to suit the needs of a particular patient. Further, data sensed during the operation of the pacemaker may be stored in the memory 100 for later retrieval and analysis.
As with the memory [0039] 44 of the ICD device 20 shown in FIG. 2, the memory 100 of the pacemaker 70 (FIG. 3) may take many forms, and may be subdivided into as many different memory blocks or sections (addresses) as needed in order to allow desired data and control information to be stored. A feature of an exemplary cardiac stimulation device is the ability to store a relatively large amount of sensed data as a data record, which data record may then be used to guide the operation of the device. That is, the operating mode of the pacemaker may be dependent, at least in part, on past performance data. For example, an average atrial rate may be determined based on the sensed atrial rate over a prescribed period of time. This average rate may then be stored and updated at regular intervals. Such stored rate may then be compared to a present atrial rate and, depending upon the difference, used to control the operating mode of the pacemaker. Other parameters, of course, in addition to (or in lieu of) atrial rate, may be similarly sensed, stored, averaged (or otherwise processed), and then used for comparison purposes against one or more currently-sensed parameters. Advantageously, modem memory devices allow for the storage of large amounts of data in this manner.
A clock circuit [0040] 103 directs an appropriate clock signal(s) to the control system 86, as well as to any other needed circuits throughout the pacemaker 70 (e.g., to the memory 100) by way of dock bus 105.
A telemetry/communications circuit [0041] 104 is further included in the pacemaker 70. This telemetry circuit 104 is connected to the control system 86 by way of a suitable command/data bus 106. In turn, the telemetry circuit 104, which is included within the implantable pacemaker 70, may be selectively coupled to an external programmer 108 by means of an appropriate communication link 110, which communication link 110 may be any suitable electromagnetic link, such as an RF (radio frequency) channel, a magnetic link, an inductive link, an optical link, and the like. Advantageously, through the external programmer 108 and the communication link 110, desired commands may be sent to the control system 86. Similarly, through this communication link 110 with the programmer 108, data commands (either held within the control system 86, as in a data latch, or stored within the memory 100) may be remotely received from the programmer 108. Similarly, data initially sensed through the leads 74 or 76, and processed by the microprocessor control circuits 86, or other data measured within or by the pacemaker 70, may be stored and uploaded to the programmer 108. In this manner, non-invasive communications can be established with the implanted pacemaker 70 from a remote, non-implanted, location.
The pacemaker [0042] 70 additionally includes a battery 93 which provides operating power to all of the circuits of the pacemaker 70 via a power signal line 95.
It is noted that the pacemaker [0043] 70 in FIG. 3 is referred to as a dual-chamber pacemaker because it interfaces with both the atria and the ventricles of the heart 77. Those portions of the pacemaker 70 that interface with the atria, e.g., the lead 74, the P-wave sense amplifier 82, the A-PG 78, and corresponding portions of the control system 86, are commonly referred to as the “atrial channel”. Similarly, those portions of the pacemaker 70 that interface with the ventricles, e.g., the lead 76, the R-wave sense amplifier 84, the V-pulse generator 80, and corresponding portions of the control system 86, are commonly referred to as the “ventricular channel”.
As needed for certain applications, the pacemaker [0044] 70 may further include at least one sensor 112 that is connected to the control system 86 of the pacemaker 70 over a suitable connection line 114. While this sensor 112 is illustrated in FIG. 3 as being included within the pacemaker 70, it is to be understood that the sensor may also be external to the pacemaker 70, yet still be implanted within or carried by the patient A common type of sensor is an activity sensor, such as a piezoelectric crystal, that is mounted to the case of the pacemaker. Other types of sensors are also known, such as sensors that sense the oxygen content of blood, respiration rate, pH of blood, body motion, and the like. The type of sensor used is not critical to the present invention. Any sensor or combination of sensors capable of sensing a physiological or physical parameter relatable to the rate at which the heart should be beating (i.e., relatable to the metabolic need of the patient), and/or relatable to whether a tachyarrhythmia is likely to soon occur, can be used. Such sensors are commonly used with “rate-responsive” pacemakers in order to adjust the rate (pacing cycle) of the pacemaker in a manner that tracks the physiological or metabolic needs of the patient.
The pacemaker [0045] 70 further includes magnet detection circuitry 87, coupled to the control system 86 over signal line 89. It is the purpose of the magnet detection circuitry 87 to detect when a magnet is placed over the pacemaker, which magnet may be used by a physician or other medical personnel to perform various reset functions of the pacemaker 70, and/or to signal the control system 86 that an external programmer 108 is in place to receive data from, or send data to, the pacemaker memory 100 or control system 86 through the telemetry communications circuits 104.
As with the ICD device [0046] 20 of FIG. 2, the telemetry or communications circuit 104 may be of conventional design, such as is described in U.S. Pat. No. 4,944,299, or as is otherwise known in the art Similarly, the external programmer 108 may be of any suitable design known in the art, such as is described in U.S. Pat. No. 4,809,697. Likewise, the memory circuit 100, and the circuits utilized in the atrial and ventricular channels may all be of common design as is known in the pacing art The present invention is not concerned with the details of the circuitry utilized for each of these pacing elements. Rather, it is concerned with the manner in which infection control signals are generated in coordination with a particular pacing mode of operation. Such coordination is controlled by the control system 86.
The control system [0047] 86 may be realized using a variety of different techniques and/or circuits. The preferred type of control system 86 is a microprocessor-based control system. It is noted, however, that the control system 86 could also be realized using a state machine. Indeed, any type of control circuit or system could be employed for the control system 86. The present invention is likewise not concerned with the details of the control systems 22 and 86. Rather, it is concerned with the end result achieved by the control system. That is, so long as the control system 86 controls the operation of the pacemaker (or other medical device) so that the desired functions are achieved as set forth herein, it matters little what type of control system is used. Those of skill in the implantable medical device art, given the teachings presented herein, should thus be able to fashion numerous different types of control systems or circuits that achieve the desired device control.
Representative of the types of control systems that may be used with the invention is the microprocessor-based control system described in U.S. Pat. No. 4,940,052, entitled “Microprocessor Controlled Rate-Responsive Pacemaker Having Automatic Rate Response Threshold Adjustment”. Reference is also made to U.S. Pat. Nos. 4,712,555 and 4,944,298, wherein a state-machine type of operation for a pacemaker is described; and U.S. Pat. No. 4,788,980, wherein the various timing intervals used within the pacemaker and their inter-relationship are more thoroughly described. The '052, '555, '298 and '980 patents are incorporated herein by reference. [0048]
Referring to FIG. 4, there is shown a diagrammatic illustration of an implanted cardiac stimulation device [0049] 120 (e.g., an ICD 20 or pacemaker 70) in combination with a pectoral implant embodying the invention including one electrode 130 in the region of the right atrium and another electrode 138 in the right ventricle of a patients heart 122. As earlier noted, microorganisms may form in a biofilm on surfaces of a housing 128 of the implanted cardiac stimulation device 120. Prior to the present invention, bacterial infections in the biofilm have been relatively untreatable without device removal since the bacteria live in the device's biofilm. The biofilm protects the bacteria from systemic antibiotics, allowing them to tolerate levels of antibiotics that are several orders of magnitude above that which can safely be given a patent.
In order to treat these infections, embodiments of the present invention use at least one electrode [0050] 130, the SVC electrode (e.g., a wire coil), which is electrically connected to the implanted cardiac stimulation device 120. The electrode 130 is implanted within the heart 122 within the region of the right atrium 132, preferably within the superior vena cava 134 leading into the right atrium 132. A first electrical current generator, e.g., the atrial pulse generator (A-PG) 78, is operable to deliver an electrical current to the electrode 130 which flows (as indicated by arrow 136) to the conductive housing 128 of the implanted cardiac stimulation device 120 in such a manner that bacteria residing in a biofilm on the implanted cardiac stimulation device 120 are destroyed. In one instance, the electrical current generator periodically generates a D.C. electrical current during the heart's refractory period. In another instance, the electrical current generator generates a high-speed square wave electrical current in a frequency range which is too rapid to affect the heart 122.
In another embodiment, a second electrode [0051] 138, the RV electrode, is electrically connected to a second electrical current generator, e.g., the ventricular pulse generator (V-PG) 80, but is instead implanted within the right ventricle 140 of the heart 122. In this instance, the first electrical current generator is operable to deliver a first electrical current to the first electrode 130 which flows (as indicated by arrow 136) to the housing 128 of the implanted cardiac stimulation device 120 following the P-wave portion of the intracardiac electrogram for the heart such that arrhythmo-genesis or parasitic pacing will not occur in the atrium. Additionally, the second electrical current generator is operable to deliver a second electrical current to the second electrode 138 which flows (as indicated by arrow 142) to the housing 128 of the implanted cardiac stimulation device 120 following the R-wave portion of the intracardiac electrogram such that arrhythmo-genesis or parasitic pacing will not occur in the right ventricle 40. By so operating (preferably in combination with a course of a biocide), bacteria residing in a biofilm on the implanted cardiac treatment device 120 are destroyed.
To obtain maximum therapeutic benefit, an average current density of about 150 microamperes per square centimeter is preferably applied to the housing [0052] 128 for a duration of about 10 hours. However, as discussed previously, this current density requires approximately a 10 ma current flow to the housing 128, a current that could pace the heart or induce an arrhythmia. Accordingly, the present invention describes two primary embodiments for dealing with this problem.
The first embodiment for solving this problem is illustrated in FIG. 5. In this first embodiment, the SVC current [0053] 136 (that is, current to electrode 130) is periodically delivered during the refractory period of the right atrium, preferably during the period of time between the P and Q wave portions of the illustrated electrogram (designated as the PQ segment). Similarly, the RV current 142 (that is current to electrode 138) is periodically delivered during the refractory period of the right ventricle, preferably during the period of time between the R and T wave portions of the illustrated electrogram (designated as the RT segment). Since the SVC current 136 is delivered following the P-wave, which is after the atria have already begun to contract and have entered a refractory period, there will be no arrhythmo-genesis or parasitic pacing in the atrium 132. Similarly, since the RV current 142 will be delivered following the R-wave, which is after the ventricles have already begun to contract and have likewise entered a refractory period, there will be no arrhythmogenesis or parasitic pacing in the right ventricle 140. While the potential for a high ventricular field generating a premature pacing event in the atria does exist this is not considered a serious side effect.
Alternatively, one could asynchronously drive the RV coil with ventricular pulses at a moderately high rate above the normal pacing rate for the patient's heart, e.g., 80 bpm, to force pacing of the patient's heart and thus there would be no need to sense R-waves. Accordingly, the timing for the infection control current pulses on the RV coil in such a VOO mode could be derived from the timing of the ventricular pulses. Similarly, an AOO mode could be used for generating infection control current pulses on the SVC coil or a DOO mode could be used for generating infection control pulses on both the SVC and RV coils. In an alternative implementation, the timing for the infection control pulses could be determined by sensing evoked P and R-wave responses to the associated pacing pulses. [0054]
FIG. 5 shows an exemplary waveform of the infection control current (solid portion) emitted by a device of the present invention when the cardiac stimulation device [0055] 120 is not generating stimulation pulses, i.e., when the heart 122 is beating within programmed limits of the cardiac stimulation device 120. In this mode, the sense amplifiers, e.g., 82 and 84, detect intrinsic P and R-waves, and this detection is used to determine the refractory period of the associated cardiac tissue, i.e., the atria or the ventricles, during which time period the associated infection control current is provided. Preferably, the associated pulse generator, e.g., 78 or 80, can be used to provide the infection control current. Alternating between the SVC and RV leads provides the additional benefit that the average current density around the device housing 128 will be slightly more homogeneous. When, pacing pulses are required (see dotted line portions), they precede the infection current pulses (from the SVC 136 and RV 142 currents) and are used to stimulate the heart as described in reference to FIG. 3. In this mode, the control system 86 can extend the stimulation pulses to the atria or ventricles, e.g., to a duration of greater than 10 ms but less than approximately 300 ms, such that the associated pulse generator, e.g., 78 or 80, can also provide the infection control current. Accordingly, the stimulation pulses will extend into the associated the refractory periods of the atria and ventricles and thus also function as current control pulses. Preferably, the same infection control apparatus can operate in both of the aforementioned modes, dependent upon whether intrinsic P and R-waves were detected during each cardiac cycle.
FIG. 6 shows an alternate embodiment In this embodiment, a high-speed square wave (shown as a solid line) is generated by pulse generators [0056] 78, 80 and preferably generates an oscillating output through each of the electrodes 130, 138 to the housing 128. Using a frequency of approximately 1-10 kHz, the pulsing is too rapid to be “felt” by the heart cells due to their slow membrane time constant response (shown as a dashed line), i.e., the heart muscles will not be stimulated by this signal. However, this higher frequency alternating current will still enhance the efficacy of the antibiotics against the biofilm.
Preferably, the present invention uses the same circuitry and leads that are already a portion of an existing cardiac simulation device. For example, when the present invention is implemented with a pacemaker [0057] 70 (FIG. 3), electrode 75 is used as the SVC electrode 130 and electrode 77 is used as the RV electrode 13B. For pacemakers operating in a unipolar mode, these leads can be driven in their normal manner and with voltage levels similar to those used for unipolar simulation (e.g., approximately 3-9 volts). For pacemakers that are implemented in a bipolar mode, i.e., in a mode where each electrode lead includes a “tip” and a “ring” (return connection), the present invention additionally includes a circuit 146 (see FIG. 2) under control of the control system 86 using signal 148 to periodically ground casing 128 during the aforementioned refractory periods when this infection control mode is activated to enable a voltage signal (e.g., 39 volts) generated at the “ip” electrode to cause a treatment current (e.g., averaging approximately 10 ma) to flow to the casing 128 in a manner similar to a unipolar mode. Additionally, the control system 86 is used to generate the timing, corresponding to the refractory periods, as shown in FIG. 5. The control system 86 uses any of the following sense amplifiers, P-AMP 82, R-AMP 84 and IEGM 85, to sense signals from the heart and thereby identify the refractory periods. The control system 86 then generates infection control signals by using this information to control any of the following pulse generators, A-PG 78 and V-PG 80, to generate programmable amplitude signals within these refractory periods. Similarly, the ICD 20 can use electrode 38 as the SVC electrode 130 and the pace generator 43 under control of the control and timing circuit 22 to generate the described infection control current during the aforementioned refractory period. Furthermore, the ICD 20 can be modified to include circuitry to generate SVC and RV infection control currents.
Preferably, the aforedescribed infection control is implemented for a period of time, e.g., 10 hours, under command from an external programmer (e.g., [0058] 48, 108 as described in reference to FIGS. 2 and 3). Actually, the treatment time is preferably extended to adjust for the combined duty cycle of the SVC and RV currents since even this combined duty cycle is still less than 100%. Alternatively, the voltage levels output by the A-PG 78 and V-PG 80 can be upwardly adjusted to accommodate for the reduced duty cycle.
In a first operational mode, this infection control mode is activated when symptoms of an infection first develop. Preferably, this infection control mode is combined with a systemic course of antibiotics, typically supplied either orally or by injection to the entire body. Due to the desired current density and treatment duration, use of the infection control mode can use a significant portion of the battery life (10 ma*10 hours=10 ma-hrs) of a typical device, e.g., approximately 10%. Accordingly, it may be desirable to use this mode only when symptoms develop. Alternatively, in a second operational mode, the infection control mode is activated soon after implantation, e.g., after initial adjustments of pacing voltage threshold levels. This second operational mode may be desirable to prophylactically avoid infections since a course of antibiotics is a normal practice following implantation surgery. Furthermore, a biocide may be additionally be supplied at the site of the implantation, e.g., surrounding the cardiac stimulation device. In this operational mode, infections may be avoided altogether (at the expense of the overall battery life of the device). [0059]
It should also be noted that in case the housing includes a separate connector top or header for connecting electrode leads to the housing as is well known in the art, for instance of the kind made of epoxy resin and molded onto the housing, the surface should be covered with a conductive coating that is in contact with the electrical current generator, directly or via the housing. [0060]
In a preferred embodiment the proximate part of the surface of the the lead is conductive and is capable of being coupled to the electrical current generator. This proximate part should extend to a position which after implantation is situated between a location beyond the entry of the lead into the venous system and the the entry into the into superior vena cava. [0061]
In this way the infection control may also be extended to the proximal parts of the lead. This may for instance be achieved by means of an electrically conducting polymer applied on said exterior surfaces of the proximal part of said lead (and also on said possible connector top). In this way traditionally non-conducting surfaces of a heart stimulator are made electrically conductive. An example of a polymer suitable for this purpose is an electrically conducting polymer marketed under the trademark ELASTOSIL. [0062]
Alternatively an electrically conducting coil is applied around said proximal part of the lead. In this way the proximal part of the lead is made not only electrically conductive but the wear resistance of the lead is improved. [0063]
The exterior surfaces of the proximal part of the lead and of said possible connector top may alternatively be treated by ion implantation technology or so-called Ion-Beam-Assisted-Deposition. This technique is especially well suited for making stimulator connector tops or headers of epoxy electrically conductive. [0064]
Other possible technologies to make a surface conducting are Physical Vapor Deposition, PVD, or Chemical Vapor Deposition, CVD or any sputtering process. [0065]
In case the housing is not made of an electrically conducting material, any of the above methods may of course be used in order to make the housing conductive. [0066]
It has been found that oxide layers, especially titanium oxide layers but also other metal oxide layers may be formed when such metals are used in the DC current environment dealt with in conjunction with the present invention. These oxide layers may cause an uneven current distribution possibly detrimental to the infection control effect. The current may also be lowered due to increased impedance caused by the oxide layer to a point at which the effect on bacteria in the biofilm is no longer effective. The formation of such oxide layers is avoided, according to an advantageous embodiment of the apparatus according to the invention, by coating the generator housing and other metallic surfaces that may become oxidized due to the DC current with one of the metals platinum, palladium or iridium or any other metal with similar electrochemical characteristics or an alloy of these metals. [0067]
While preferred embodiments of the invention have been disclosed in detail, it should be understood by those skilled in the art that various other modifications may be made to the illustrated embodiments without departing from the scope of the invention as described in the specification and defined in the appended claims. For example, implementations using: atrial SVC or ventricle RVC leads alone or in any combination are considered to be within the scope of the present invention. Furthermore, while it is desirable to use the same circuitry and control leads as an implanted cardiac stimulator to generate the infection control currents, implementations which use additional leads and circuitry to generate the aforedescribed infection control currents are also considered to be within the scope of the present invention. [0068]
1. A cardiac stimulating device for stimulating a patient's heart comprising an infection control apparatus, the cardiac stimulating device comprising:
detection apparatus for determining a refractory period following the heart's stimulation;
a controller for periodically causing the electrical current generator to generate an infection control current during said refractory-period; the entire external surface of said device being electrically conductive;
a switching means for connecting said external surface to said current generator;
said stimulating device being connectable to at least one heart electrode lead whose electrode Is adapted to be implanted close to the patients heart,
said heart electrode lead's surface at the part proximate to the stimulating device being conductive and being capable to be connected to said current generator,
said proximate part extending to a position which after implantation is situated at a location beyond the entry into the venous system and before the entry into the superior vena cava,
said electrode being connected to said current generator for receiving the infection control current which flows from the conductive external surface and proximal part of the heart electrode lead to treat infections surrounding the external surface of said cardiac stimulating device.
2. The cardiac stimulating device according to claim 1, wherein the device comprises a housing with an electrically conductive external surface and a header or connector top with an external electrically conductive surface.
3. The cardiac stimulating device of claims 1-2, wherein the infection control current generator is used in combination with a biocide.
4. The cardiac stimulating device of claims 1-2, wherein the infection control current generator is used in combination with systemic application of antibiotics to the patient's body.
5. The cardiac stimulating device of claims 14 wherein the infection control current generator is remotely activated.
6. The cardiac stimulating device of claim 5, wherein the infection control current generator is activated upon detection of an infection.
7. The cardiac stimulating device of claims 1-4, wherein the infection control current generator is prophylactically activated upon implantation of the stimulating device.
8. The cardiac stimulating device of claims 1-7, wherein the electrical current generator, detection apparatus, and controller correspond to the other circuitry shared by the cardiac stimulating device.
9. The cardiac stimulating device of claims 1-8, wherein the electrode corresponds to an electrode used by the cardiac stimulating device for sensing/stimulating the patient's heart.
10. The cardiac stimulating device of claims 1-9:
a first electrode implanted within the heart's right atrium; and
a second electrode implanted within the heart's right ventricle;
wherein the at least one current generator comprises;
a first current generator for driving the first electrode; and
a second current generator for driving a second electrode;
wherein the detection apparatus comprises;
11. The cardiac stimulating device of claims 1-9, wherein the detection apparatus is a sense amplifier which detects the refractory period of the right atrium by sensing an intrinsic P-wave.
12. The cardiac stimulating device of claims 1-9, wherein the detection apparatus is a sense amplifier which detects the refractory period of the right atrium by sensing an evoked P-wave.
13. The cardiac stimulating device of claims 1-9 wherein the detection apparatus is a sense amplifier which detects the refractory period of the right ventricle by sensing an intrinsic R-wave.
14. The cardiac stimulating device of claims 1-9 wherein the detection apparatus is a sense amplifier which detects the refractory period of the right ventricle by sensing an evoked R-wave.
15. The cardiac stimulating device of claims 1-9, wherein the detection apparatus determines the refractory period according to a time period following stimulation of the patient's heart.
16. The cardiac stimulating device of claims 1-15, wherein the cardiac stimulating device is a pacemaker.
17. The cardiac stimulating device of claim 16, wherein at least one electrode operates in a bipolar mode.
18. The cardiac stimulating device of claims 1-15, wherein the cardiac stimulating device is an implantable cardioverter defibrillator (ICD).
19. A cardiac stimulating device for stimulating a patient's heart comprising an infection control apparatus, the cardiac stimulating device comprising:
at least one electrical current generator for generating a square wave infection control current;
the entire external surface of said device being electrically conductive;
said external surface being being capable of being coupled to said current generator;
said stimulating device being connectable to at least one heart electrode lead whose electrode is implanted close to the patient's heart,
said heart electrode lead's surface at the part proximate to the stimulating device being conductive and being capable to be connected to said square wave current generator,
said electrode being connected to said square wave current generator for receiving the infection control current which flows from the conductive housing and proximal part of the heart electrode lead to treat infections surrounding the pulse generator housing.
20. The cardiac stimulating device according to claim 19, wherein the device comprises a housing with an electrically conductive external surface and a header or connector top with an external electrically conductive surface.
21. The cardiac stimulating device of claim 19, wherein the square wave current is at a frequency in the range of 1 to 10 kHz.
22. The cardiac stimulating device of claims 19-21, wherein the infection control current generator is used in combination with a biocide.
23. The cardiac stimulating device of claims 19-21, wherein the infection control current generator is used in combination with systemic application of antibiotics to the patient's body.
24. The cardiac stimulating device of claims 19-23 wherein the infection control current generator is remotely activated.
25. The cardiac stimulating device of claims 19-24, wherein the infection control current generator is activated upon detection of an infection.
26. The cardiac stimulating device of claims 19-24 wherein the infection control current generator is prophylactically activated upon implantation of the stimulating device.
27. The cardiac stimulating device of claims 19-26, wherein the electrode corresponds to an electrode used by the cardiac stimulating device for sensing/stimulating the patient's heart.
28. The cardiac stimulating device of claims 19-27, wherein the cardiac stimulating device is a pacemaker.
29. The cardiac stimulating device of claims 19-27, wherein the cardiac stimulation device is an implantable cardioverter defibrillator (ICD).
US10468867 2001-02-27 2002-02-26 Implantable medical device with a current generated for infection control Expired - Fee Related US7203550B2 (en)
SE0100669-1 2001-02-27
SE0100669A SE0100669D0 (en) 2001-02-27 2001-02-27 implantable device
PCT/SE2002/000345 WO2002068049A1 (en) 2001-02-27 2002-02-26 Implantable device
US20040098055A1 true true US20040098055A1 (en) 2004-05-20
US7203550B2 US7203550B2 (en) 2007-04-10
ID=20283149
US10468867 Expired - Fee Related US7203550B2 (en) 2001-02-27 2002-02-26 Implantable medical device with a current generated for infection control
US (1) US7203550B2 (en)
EP (1) EP1365838B1 (en)
DE (1) DE60204286T2 (en)
WO (1) WO2002068049A1 (en)
EP1365838B1 (en) 2005-05-25 grant
DE60204286D1 (en) 2005-06-30 grant
US7203550B2 (en) 2007-04-10 grant
DE60204286T2 (en) 2006-02-02 grant
WO2002068049A1 (en) 2002-09-06 application
EP1365838A1 (en) 2003-12-03 application
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:KROLL, MARK;ECKERDAL, JOHAN;OBEL, MARTIN;AND OTHERS;REEL/FRAME:015125/0910