Body bus medical device communication system

Abstract: A system intended for being at least partly implanted into a living body and comprising at least two modules or devices (10, 42) which are interconnected by a communication transmission channel, at least one of said modules (10) being provided with transmitting (27) and receiving (26) means for a bidirectional exchange of information with at least one further module and at least one other module (42) of which being provided at least with receiving means (34) or transmitting means (35) for receiving information from at least one further module or for transmitting information to at least one further module, respectively. Within the intracorporal region, said communication transmission channel is wireless. It includes the ion medium of the intra and extracellular body liquids and provides for an electrolytic-galvanic coupling between two or more implantable modules and/or between at least one implantable module (10) and external skin electrodes (40, 41) intended for connection to an external module (42). The exchange of information is effected by modulated medium frequency signals in the frequency range from 10 to 100 kHz which signals are passed through said communication transmission channel.

Description: This invention relates to a system of medical devices intended for being at least partly implanted into a living body and comprising at least two modules which are interconnected by a communication transmission channel denoted the "body bus". Devices of this type are known in different embodiments, e.g. EP-A-0 011 935 and EP-A-0 011 936 describe an external programming device and an implantable electromedical device adapted for being programmed thereby, wherein the programming device comprises a transmitting antenna, and the implantable device comprises a receiving antenna which are mutualy aligned with each other for programming in order to transcutaneously transmit high frequency programming signals in the form of electromagnetic waves from the transmitting antenna to the receiving antenna. In view of the fact that high frequency electromagnetic waves are heavily attenuated or screened by body tissue, the implanted receiving antenna must be exactly located for programming. Such a procedure is particularly troublesome if a plurality of programmable modules, e.g. a pacemaker, a defibrillator and a drug dispensing device, are implanted, the receiving antennas of which must be individually located. In the case of a prior muscle stimulation apparatus (US-A-4,524,774) in a similar manner, muscle potentials detected by implanted sensors are converted by a modulator into control signals for a telemetry transmitter which is integrated into the respective sensor. This telemetry transmitter transcutaneously transmits high frequency telemetry signals to an external telemetry receiver which is connected to a data processing unit. The latter, on the basis of the received signals, controls a likewise externally disposed telemetry transmitter for delivering high frequency control signals, again transcutaneously, to receivers of implanted muscle stimulators. The transcutaneously transmitted signals are in the megacycles/sec. frequency range so that the aforementioned restrictions are encountered in this case too. Furthermore, it is known (Fig. 1 of US-A-4,543,955) to transmit measuring signals of an implanted sensor module through a wire connection to another implanted module, such as a pacemaker or a drug delivery device. This requires, during implantation, a troublesome wiring of connection conduits. Furthermore if an infection occurs at one of the implanted modules, all modules and connection conduits must be removed because the infection can spread along the connection conduits. In conformity with modified embodiments of the last mentioned device (Figs. 2 and 5 of US-A-4,543,955) measuring signals, which have been converted into a program code, also can be unidirectionally transmitted, in a wireless manner, from the sensor to the pacemaker or to the drug dispensing device, wherein either the signals defining the program code are directly transmitted through body tissue (i.e., without any carrier) or again a high frequency transmitter is used. A carrier free signal direct transmission, for being effective, must be carried through during the refractory phases, i.e. must be synchronized with the heart cycle because otherwise the signals required for such a direct transmission may provoke undesired biological reactions. On the other hand, the high frequency transmission, in this case too, poses problems because of the heavy attenuation caused by body tissue and is possible, if at all, merely if the transmitting and receiving antennas are closely spaced within the body. The object basic to the invention is to provide for a device of the type mentioned at the beginning which allows a signal transmission between the modules in a particularly simple, reliable and universally applicable manner while simultaneously avoiding the above discussed deficiencies. The invention is defined by claim 1. The features of the preamble of claim 1 are known from US-A-4,313,441. A modulated signal in the frequency range from 10 kHz to 100 kHz has a sufficiently high frequency to not cause any polarisation problems within the living body and to allow an effective filtering with high Q filters requiring only little installation space. On the other hand, this frequency range is so low that undesired high frequency phenomena, such as radiation problems, crosstalk and excessive attenuation of the desired signals by the body tissue are avoided. Rather, modulated signals in the frequency range from 10 to 100 kHz are electrolytically-galvanically transmitted over the distances encountered in the living body with such a low attenuation that on the transmitter side signal amplitudes which biologically are certainly ineffective and which can be transmitted without any regard to the heart cycle also to electrodes which might be provided for stimulation of the heart are sufficient to allow the modulated signals to be reliably detected at the receiver side at low expenditure for filters and amplifiers. The implantable devices may be a cardiac pacemaker and a defibrillator. In conformity with a development of the invention, a discrete medical device is provided external to the body for bi-directional communication with one implantable device, e.g. a cardiac pacemaker. A bi-directional exchange of information provides for an interactive mutual coupling of the individual modules. The functional interconnection between implanted and external modules is obtained in a particularly simple manner via body fluids by making use of the electrolytic-galvanic coupling, presently also shortly named body bus, and via skin electrodes so that a troublesome search for the antennas of the implanted module or modules is avoided. In conformity with a further development of the invention, at least one digitally programmable implantable module and an external module in the form of a programming device are provided. The programmer would, because of the body bus bi-directional properties, enable interactive intelligent programming. Over a modem, telephone programming and control would be possible, especially a necessity for endangered tachy or defibrillator patients. Preferred examples of implanted modules are nerve stimulators, muscle stimulators, cardiac pacemakers, defibrillators, drug dispensing devices, sensors for detecting body parameters or body activities as well as controllable and/or programmable artificial organs. Apart from the aforementioned programming devices, particularly, but not exclusively, monitoring and/or test devices may be used as external modules such as data recording devices (magnetic tape devices or the like) or modems adapted for connection to telephone circuits. If a plurality of implantable modules are provided, programming and/or intelligent decision means, in conformity with a further development of the invention, preferably are concentrated in one of the implanted modules only wherein, in case of need, other implanted modules can be indirectly programmed via said one module. Thereby, it is possible to keep the hardware expenditure, the weight, the space requirements and the energy consumption of the total of implanted modules particularly small. Basically, however, it is likewise possible to provide a plurality of implanted modules comprising programming and/or intelligent decision means which modules mutually communicate via the body bus. Preferably the modules are provided with means for receiving and/or transmitting of pulse code-modulated medium frequency signals. A1-modulated medium frequency signals may be used, i.e. the signal has a single, fixed frequency of e.g., 30 kHz, and this signal, at the transmitting side, is switched on and off as a function of the modulation. In conformity with a modified embodiment, the modules may be provided with means for receiving and/or transmitting signals which are frequency shifted between a pair of frequencies within the medium frequency range. That means a pair of predetermined fixed signal frequencies, e.g. of 30 kHz and 40 kHz are used, and shifting takes place at the transmitting side between the two signal frequencies as a function of the modulation. The pulse code modulation avoids sidebands and continuous frequency swings. The one or the two signal frequencies can be generated at the transmitting side by means of crystal oscillators with a high frequency accuracy and high frequency stability whereas at the receiving side, narrow-banded amplifiers which e.g. are provided with crystal filters and which are tuned to the signal frequency or the signal frequencies, may be provided. The invention has a multiplicity of advantageous applications. For example, tachycardiac rhythm disturbances so far at first are treated with drugs. On further progress of the disease, antibradycardiac stimulation by means of a sequential pacemaker of a known type may become necessary, wherein simultaneously or at a later state it may be advantageous to supplement the antibradycardiac stimulation by antitachycardiac stimulation pattern (compare e.g. EP-A-0 094 758). When this too is no longer sufficient to adequately influence the syndrome and attacks of ventricular fibrillation occur, a defibrillator becomes necessary which likewise is available as an implantable device. However, when implanting the defibrillator, the sequential pacemaker again must be explanted because this pacemaker delivers atrial and ventricular stimulating pulses which, in the same manner as possibly the R-wave of the electrocardiogram, too, are detected by the defibrillator whereby the latter sees an apparent frequency duplication or frequency triplication. When the heart works correctly with e.g. 70 beats per minute, therefore, there is the risk that the defibrillator detects an apparent heartbeat rate of 140 or 210 beats per minute and undesirably delivers a defibrillation pulse. When the pacemaker is explanted, necessarily the antibradycardiac and possibly also antitachycardiac protective effect thereof no longer exists. Besides, the drug dosage must be reduced because the patient no longer is protected against a drop of the rate of the heart activity. The defibrillator will become active relatively frequently and possibly inappropriately. Within the scope of the present invention, it is possible to transfer the intelligent decisions, particularly the detection of the requirement of a defibrillation shock, from the defibrillator to the preferably A-V sequential, programmable, microprocessor based pacemaker and to make the defibrillator only indirectly programmable via the pacemaker making use of the body bus. The pacemaker which e.g. may be designed in the manner known from EP-A-0 094 758, safely detects whether the pacemaker itself stimulates or whether there is a tachycardia. When a tachycardia is detected, the pacemaker can request the shock from the defibrillator through the body bus. Therefore, if in the course of the therapy the sequential pacemaker no longer will be sufficient, this pacemaker need not be explanted. Rather the therapy can be systematically built up as a function of the respective requirements without previous implants becoming obsolete. In view of the monitoring functions included in the pacemaker, the requirement of the additional implantation of a defibrillator function can be detected at an early state. The defibrillator, which constitutes a high current application, then can be added. Simultaneously, the sequential antibradycardial stimulation, possibly assisted by drugs, reduces the fibrillation incidence when compared with a pure ventricular stimulation. The stimulation treatment of tachycardia likewise can be carried through by the pacemaker, optionally in a dual chamber manner, whereby the effectivity of detection and of the treatment is increased thereby again reducing the probability of fibrillation. Thus the defibrillator may be restrained, as far as conceivable, to its function as an emergency or backup system. With respect to the separation of pacemaker and defibrillator, which is easily possible by making use of the body bus, it is to be taken into consideration that the pacemaker, particularly if, in a manner known per se, it is microprocessor controlled and programmable and also includes antitachycardiac algorithms, constitutes a complex and therefore relatively expensive device which, however, merely has a low current consumption and therefore has a very long duration even if the housing volume, as desired, is small. Besides, the pacemaker may be implanted at many different body sites as a function of appropriateness. Different therefrom, a defibrillator has a high energy consumption and, if it was only in view of its storage capacitors, a large volume. It can be implanted at a few body sites only, and in view of its high energy drain, has a relatively short lifetime. Moreover, recent clinical studies of patients implanted with AICD devices indicate that in a large number of such patients, the defibrillation shock is delivered quite infrequently, i.e. two to four times a year. Despite the infrequent delivery of the shocks, the AICD units need to be replaced within two years due to the deterioration of the batteries. The system of the present invention contemplates the possibility of replacing a large volume, large capacity defibrillator with a small volume low capacity (in other words, a limited number of shocks) in those patients where experience has shown that the patient only infrequently requires a defibrillation shock. It can be expected that in even those patient populations, the frequency of required defibrillation shocks will be diminished by the efficacy of antitachycardia pacing therapies delivered by the separate pacemaker unit. Thus the present invention contemplates the provision of a staged therapy to the patient first involving the implantation of an intelligent pacemaker in the patient and then, if necessary, the additional implantation of a defibrillator having a shock delivery capacity tailored to the requirements of the patient, e.g. 10, 20, 100 shocks per year at maximum programmable output energy. Therefore, for all these reasons, normally it does not make sense to combine the pacemaker and the defibrillator in one and the same casing. In addition, the body bus system components may include separate remote sensors for physiologic rate responsive pacing and/or detection of arrhythmias (to augment or replace the electrogram sensing employed to confirm malignant VT or VF) as well as a drug dispenser. The drug may be delivered into the patient's body or the patient's vascular system as is appropriate to treat the patient in a fashion which the pacemaker electronics would find appropriate. For treatment of an arrhythmia detected by the pacemaker, the drug may be delivered into the vascular system or a chamber of the heart or into the body of the patient in conformance with the appropriate delivery of the specific drug. Fig. 1 is a schematic circuit diagram of a cardiac pacemaker adapted for being programmed via the body bus; Fig. 2 is a schematic diagram of a body bus transmitter; Fig. 3 is a schematic circuit diagram of a body bus receiver; Figs. 4 and 5 illustrate embodiments of devices designed in conformity with the present invention; and Fig. 6 illustrates the experimental setup prepared to demonstrate body bus signal transmission. Fig. 1 shows an implanted microprocessor controlled, programmable cardiac pacemaker 10 comprising a central processing unit (CPU) 11, a random access memory (RAM) 12, a read-only memory (ROM or EPROM) 13, a battery 14 and an input/output unit (I/O) 15. The input/output unit includes amongst others a coder and a decoder for coding and decoding, respectively, of serial information to be exchanged between the cardiac pacemaker 10 and other implantable or external modules, in the illustrated embodiment an external programming unit 42. Such programmable pacemakers and associated programming devices e.g. are known from EP-A-0 011 935 and EP-A-0 011 936; they, therefore, presently need no further explanation. The input/output unit 15 is connected through an input or sensing amplifier 18 and an output amplifier 19 to the atrial electrode 20 of a pacemaker lead 21; besides it is connected through an input or sensing amplifier 22 and an output amplifier 23 to a ventricular electrode 24 of the pacemaker lead 21. A body bus receiver 26 is connected to a further input of the input/output unit 15, whereas an additional output of the input/output unit is connected to a body bus transmitter 27. The input of the body bus receiver 26 is connected to the ventricular electrode 24 and to an indifferent electrode 28 which preferably is defined by the casing of the pacemaker 10. The ventricular electrode 24 and the indifferent electrode 28 furthermore are connected to the output of the body bus transmitter 27. The ventricular electrode 24 and the indifferent electrode 28 form a transmitting and receiving dipole for the pacemaker 10. However, the atrial electrode 20 and the indifferent electrode 28 likewise can be used to define the transmitting and receiving dipole of the pacemaker 10. The heart is indicated at 29. The programming signal processor 16 is connected via an input/output unit 32 to a body bus receiver 34 and to a body bus transmitter. Inputs 36, 37 of the body bus receiver 34 and outputs 38, 39 of the body bus transmitter 35 are connected to external skin electrodes 40 and 41, respectively, which are put around the wrist joints of the patient. The unit 16, together with units 32 to 35, forms an external programming device 42 having a transmitting and receiving dipole defined by electrodes 40 and 41. The body bus transmitters 27, 35 may be designed in the manner illustrated in the schematic circuit diagram of Fig. 2. The transmitter includes an oscillator 43, preferably a crystal oscillator, which generates a preferably sinusoidal carrier signal having a fixed predetermined frequency in the medium frequency range extending from 10 kHz to 100 kHz. The oscillator 43 is keyed, in conformity with an A1-modulation, by a serial modulation signal 45 supplied to an input 44. The oscillator correspondingly supplies at its output a modulated medium frequency carrier signal 46 consisting of groups of each a plurality of carrier oscillations. The modulated carrier signal is supplied to the input of an output unit 47 which includes a transistor 48 which delivers across an output resistor 49 an amplified modulated carrier signal having an amplitude of preferably 50 to 500 millivolts, e.g. about 200 millivolts. A design suitable for the body bus receivers 26 and 34 schematically is illustrated in Fig. 3. The receiver, at the input side thereof, includes a preamplifier 50, e.g. an amplifier comprising an octocoupler. Preamplifier 50 is follows by a high-Q filter 51, preferably a crystal filter, which is tuned to the carrier frequency of e.g. 30 kHz. Filter 51 provides a narrow passband for the carrier signal and substantially suppresses signals of all other frequencies. Filter 51 is followed by a further amplifier unit 52 and a demodulator and pulse shaping unit 53 which converts the received filtered groups of carrier signal oscillations 54 into pulses 55 of predetermined amplitude and a duration defined by the code. Returning to Fig. 1, in order to program the implanted pacemaker, i.e. for setting or changing parameters such as the rate, the amplitude and the width of the stimulation pulses, the sensitivity of the input amplifiers 18, 22, the refractory period, the detection algorithm for detecting arrhythmias (rate, onset/acceleration, number of intervals to trigger, etc.) and the like and/or for selecting one of a plurality of possible pacemaker modes, the electrodes 40, 41 are applied at a desired site of the patient, e.g. at the wrist joints, and serially coded programming commands in the form of the modulated medium frequency carrier signal are supplied to the electrodes 40, 41 from the programming unit 42 via the input/output unit 32 and the body bus transmitter 35. The transmitter dipole defined by electrodes 40, 41 transcutaneously introduces the modulated carrier signal into the body of the patient. There the signal is propagated in the ion medium of the intra and extracellular body liquids. In this manner, the modulated carrier signal is transmitted by electrolytic-galvanic coupling to the receiving dipole defined by the ventricular electrode 24 and the indifferent electrode 28 of the pacemaker 10. The modulated carrier signal then is amplified, filtered, demodulated and shaped in the body bus receiver 26 and is decoded via input/output unit 15 for further processing. In a corresponding manner the programming device 42 can request from pacemaker 10 information for purposes of monitoring, repeating and remote indicating or the like. This information, again in serially coded form, is communicated from the input/output unit 15 to the body bus transmitter 27 where it modulates a medium frequency carrier signal. The modulated carrier signal is applied by the transmitting dipole defined by electrodes 24, 28 to the ion medium of the body, is propagated there and transcutaneously reaches the electrodes 40 and 41 of the programming device 42 which electrodes now act as a receiving dipole. The modulated medium frequency signal is filtered out in a narrow band mode, is amplified, demodulated and shaped and finally is processed via decoding in input/output unit 32 for being applied to the signal processor unit 16 for decoding, storage and display. Whereas the transmitters and receivers of Figs. 2 and 3 are designed for an A1-modulation, other modulation modes, particularly a pulse code modulation with shifting between a pair of carrier signal frequencies within the frequency range from 10 kHz to 100 kHz (so-called FSK-modulation) likewise can be used for the body bus receivers 26, 34 and the body bus transmitters 27, 35. The arrangement of Fig. 1, even still afterwards, easily can be further expanded, e.g. by implantation of a defibrillator 58, as schematically illustrated in Fig. 4. The defibrillator 58 comprises a defibrillator output unit 60 adapted to be charged from a battery 59, the output side of unit 60 being connected to implanted defibrillator electrodes 61 and 62. The defibrillator output unit 60, at the input side thereof, is controlled through a body bus receiver 63 and a decoder 64 connected to the output of the latter. The inputs of the body bus receiver 63, which e.g. is designed in conformity with Fig. 3, likewise are connected to the defibrillator electrodes 61, 62 which simultaneously function as receiving dipole of the body bus. The defibrillator 58 together with its associated battery 59 is housed within its own casing, and it can be implanted at a suitable site remote from the pacemaker 10. Defibrillator 58 is controlled by pacemaker 10 which, for this purpose, is provided in a manner known per se (e.g. in conformity with US-A-4,548,209 and EP-A-0 094 758) with tachycardia and/or fibrillation detection means and, if desired, likewise with means for providing antitachycardiac pacing stimulation pattern, e.g. overdrive, burst or ramp stimulation as is known in the art. In this connection, also means for indirectly programming the defibrillator through the pacemaker 10 and the body bus may be provided. The body bus permits one to intelligently employ the defibrillator 58 which itself does not comprise means for sensing and for making decisions. For example, provisions can be made by a corresponding software design of the microprocessor controlled pacemaker 10 that in case of ventricular tachycardia which cannot be interrupted by means of the pacemaker 10 at first a cardioversion attempt with low energy is caused, whereas in the case of the occurrence of ventricular fibrillation, immediately high energy defibrillation is effected by the defibrillator 58 which is correspondingly controlled by pacemaker 10. Instead of programming pacemaker 10 by the programming device 42 connected to the skin electrodes, or in addition thereto, programming of pacemaker 10, in conformity with Fig. 4, likewise can be effected through the telephone circuit by means of a simple auxiliary device in form of a modem 66. Modem 66 includes a body bus receiver 68 and a body bus transmitter 69 which, in turn, are connected to external skin electrodes 70 and 71. Modem 66 e.g. can be designed as a modified telephone receiver having a first hand electrode 70 at the receiver and a separate second wrist joint electrode 71. By a corresponding software design, pacemaker 10 at first can test, with the aid of test signals, the data transport rate of the used telephone network to subsequently automatically adjust the body bus transmitter 69 to the data rate adapted to be communicated. The surface ECG can be directly transmitted to the skin electrodes 70, 71. Selectively, however, it is likewise possible to make sure that all data are communicated through the body bus and that, therefore, the intracardiac ECG is telemetered. Body bus data can be derived through electrodes 70 and 71 for further purposes, e.g. all data which anyway occur in pacemaker 10 can be communicated through the telephone circuit. Data monitoring and keeping of data archives likewise is possible. Thus, in view of the fact that the medium frequency range is used, a tape recorder 72 can be connected to the skin electrodes 40, 41 or 70, 71 in order to record the body bus signals which subsequently can be centrally evaluated by a processor or computer. Fig. 5 illustrates a further embodiment in which the defibrillator 58, too, bidirectionally receives and delivers data. For this purpose, a body bus transmitter 74, is provided in addition to the body bus receiver 63. Transmitter 74 and receiver 63 are connected to the defibrillator output unit 60 through an input/output unit 75 which provides for the necessary coding and decoding of the signals. Such a design allows more complicated software structures of the defibrillation protocol. For example, the pacemaker 10, in case of an impending fibrillation, as a precaution, can request the defibrillator 58 to make available a shock which is not delivered to the body until the defibrillator 58 informs the pacemaker that the shock energy is ready. The pacemaker, in response to further monitoring of the heart activity, can decide whether or not the shock is to be delivered to the heart. When the shock, made ready as a precaution, is not required, the pacemaker 10 can deliver a corresponding command to the defibrillator 58, which command causes that the storage capacitor of the defibrillator is slowly discharged or that the energy stored in the storage capacitor is returned through a converter into the defibrillator battery 59, which in this case is rechargeable, in order to save energy. It is also possible that the pacemaker 10 applies possibly dangerous antitachycardiac stimulation modes not before it has made sure through the body bus that in case of an emergency the shock immediately will be available. Fig. 5 further schematically illustrates an implantable drug delivery device 77 including a battery 78, a body bus receiver 79, a decoder 80 and a drug pump 83. The casing of the device forms a first electrode 81 connected to an input of the receiver 79, whereas a further electrode 82 is connected to a second input of receiver 79. Electrode 82 together with electrode 81 forms an implanted receiving dipole. If required, pacemaker 10 can order, through the body bus, the drug delivery device 77 to deliver a bolus of a drug. Device 77, in a manner similar to defibrillator 58 of Fig. 5, likewise can be designed for a bidirectional exchange of information to allow replies to the pacemaker 10. Fig. 5 finally illustrates a remote physiologic sensor 84 included in the body bus system, which sensor comprises a battery 85, a coder 86, a body bus transmitter 87 and a sensor and its associated circuitry. An output of the body bus transmitter 87 is connected to a first electrode 88 defined by the sensor casing, whereas a second input of the body bus transmitter 87 is connected to an auxiliary electrode 89. Electrodes 88 and 89 form a transmitting dipole of the sensor. The sensor, in a manner known per se, is adapted to sense respiration body activity or body parameters such as arterial blood pressure, temperature, pH value, pO₂ value and the like. Corresponding signals are telemetered to the pacemaker 10 through the body bus for suitably influencing the pacemaker. For example, the sensor data may be used to confirm the existence and nature of a bradyarrhythmia or tachyarrhythmia to influence the selection of the therapy by the pacemaker, drug dispenser or defibrillator and to influence the rate of bradyarrhythmia pacing. The sensor likewise can be designed for a bidirectional exchange of data. In this case it will e.g. be possible to let the pacemaker 10 control sensor characteristics such as the sensitivity of the sensor. It is evident that the invention can be further modified in many different ways. For example, it is possible to at first implant an AAI pacemaker provided with body bus characteristics. If later on an AV block requires ventricular stimulation, a VVI pacemaker with body bus may be additionally, e.g. myocardially, implanted. The VVI pacemaker and the AAI pacemaker, by exchanging information therebetween, can cooperate to provide for a DDD function. A further possible application is the implantation of a pacemaker having dp/dt functions for controlling pacing rate as a function of blood pressure rate of change. In such a case, information for delivering from a simultaneously implanted drug delivery device a drug influencing the blood pressure can be transmitted through the body bus. Thereby a "closed loop" system for blood pressure control is realized. It is apparent that in each case suitable protocols for the data transmission, for securing priorities, for providing for redundancy and the like, are to be used. The body bus receivers likewise, in a manner known per se, may be provided with an automatic gain control (AGC). An experimental setup prepared by the inventor to test the practicality of the body bus communication system proposed above is illustrated in Fig. 6 and comprises a physiologic saline test tank 100, two personal computers 102 and 104, a pacing lead 106 having a pair of distal electrodes 108, 110 located within the saline solution, a pair of plate electrodes 112, 114 and transmitting and receiving interconnecting circuitry. The transmitting computer 102 is coupled to the proximal terminals of the pacing lead 106 by the crystal oscillator 43', 47' corresponding to the transmitter circuit of Fig. 2 and a further optocoupler 116. Similarly, the plate electrodes 112 and 114 are coupled to the two inputs of an optocoupler and preamplifier 50', the output of which is coupled to the pulse former circuitry 51', 52', 53' which collectively correspond to the receiver circuit of Fig. 3. The output signal of the pulse former 51', 52', 53' is applied to the second personal computer 104. The plate electrodes 112 and 114 were prepared from copper plates each having a surface of approximately 64cm² to electrically imitate one type of implantable defibrillator leads. The electrodes 112, 114 are placed apart a distance approximating the distance that defibrillating plate electrodes are normally spaced across the heart in actual implantations in patients. The standard endocardial bipolar pacing lead 106 is placed so that its bipolar electrodes 108, 110 are between the plate electrodes 112, 114 to approximate the location within a patient's heart. The tank 100 is filled with physiological saline solution. The experiments were conducted to test the hypothesis that useful information could be transmitted in both directions through the conducting medium between the pacing electrodes 108, 110 and the defibrillation electrodes 112, 114. With the 8032 based Commodore personal computer, text was entered by its keyboard which is converted into the corresponding ASCII-NR. code which is written as an 8-bit byte into a memory location. This byte is then converted into a serial train of bit pulses preceded by a leader pulse and is emitted from its cassette port so as to gate the output of the signal generator 43', 47' at 30 kHz. With an appropriate level (200 mV) these 30 kHz burst pulses are fed through the optocoupler 116 to a Medtronic bipolar Model 6901 lead 106 immersed in the physiologic saline solution. The signals are shown illustrated at points A and B in Fig. 6, the leader illustrated as the initial wide burst signal. Pulse width modulation was employed to encode the stream of bits emitted by the electrodes 108, 110 into the saline solution. The signals emitted from the bipolar pacing electrodes 108, 110 travel through the saline solution and are picked up by the defibrillator electrodes 112, 114 and applied to the input terminals of the optocoupler in preamplifier 50'. The signal level at the input terminals of the optocoupler amplifier 50' is approximately 3 mV. After filtering and amplification by the optocoupler preamplifier 50' and pulse former 51', 52', 53', the lower edge envelope curve is reconstructed so that at this stage, the serial 8 bit pulse train with its leader can be applied to an input port or user port of a second 8032 Commodore personal computer. After serial to parallel conversion, the received code is displayed on the computer screen. During testing, the removal of the pacing lead 106 from the saline solution during transmission of the code between the transmitting computer 102 and receiving computer 104 interrupted and terminated the transmission. Thus the transmission is obtained by the bulk conductivity of the saline solution. Moreover, by reversing the electrode connections, information could just as easily be transferred from the defibrillator plate electrodes as the transmitting electrodes to the pacing electrodes 108, 110. Various experiments were conducted with the orientation of the electrodes 108, 110 to the electrodes 112 and 114 wherein it was found that the only orientation that became insufficient was when the transmitting dipole provided by the pacing electrodes 108, 110 was directly perpendicular to the receiving dipole provided by the electrodes 112, 114 (or conversely). With conformal defibrillation electrodes 112, 114 and the usual orientation of a bipolar pacing lead axially within the heart's right ventricle, it is unlikely that this insufficient orientation would be encountered in practice. A second bipolar electrode was connected to the output and can of a Medtronic Model 8423 VVI pacemaker which was also put into the bath of saline in tank 100. The pacemaker could not be inhibited by the high frequency 30 kHz bursts being delivered through the saline medium. This test confirmed the proposition that the 30 kHz signal at the 200 mV amplitude did not mimic signals normally sensed by a pacemaker and thereby interfere with its normal operation. The waveform used, even switched at rates at about 80 bpm, would not inhibit a standard VVI pacemaker. In tests conducted with this experimental setup, it was determined that the burst pulse modulation with a carrier in the range of 30 kHz enabled the propagation of ASCII code safely, easily and rapidly through the conductive medium of the test tank 100. The frequency and voltage related current levels employed allow for the use of already implanted heart stimulation leads without the need of synchronization into the refractory periods of the pulse generators. Since there are no side bands, extremely narrow pass amplification of the received signals would make electrical noise suppression very simple. The baud rate can exceed 400 bauds. Since the transmission speed is higher than any imaginable intracorporeal need, a high degree of safety can be achieved by redundant transmission and other forms of data encription. A computer listing actually used to transmit the statement "the quick brown fox jumps over the lazy dog" between the transmitting and the receiving personal computers is attached hereto as follows: From the foregoing description, it will be apparent that the body bus system of the present invention has a number of advantages, some of which have been described above and others of which are inherent in the invention. Also it will be apparent that modifications can be made to the system. Accordingly, the scope of the invention is only to be limited by the accompanying claims.

Claims: A system for monitoring a condition of a living body and/or providing a therapy regimen to the body, comprising one discrete medical device (10) adapted to be implanted into the body, said one discrete medical device including transmitting means (27) for applying a first information signal to a pair of electrodes (24, 28) of the implantable device, said one discrete medical device further including receiving means (26) for receiving a second information signal via said pair of electrodes (24, 28), characterised by at least one further discrete medical device (58; 77; 84) adapted to be implanted into the body that includes means (63, 74; 79; 87) providing at least uni-directional communication with said one implantable device (10) by receiving said first information signal or transmitting said second information signal, via a pair of electrodes (61, 62; 81, 82; 88, 89) of the further implantable device, said at least uni-directional communication by the transmission of said first information signal or the transmission of said second information signal comprising the conduction of a modulated signal in the frequency range from 10 to 100 kHz through the ion medium of the intra- and extra-cellular body fluids by means of electrolytic-galvanic coupling between the respective pairs of electrodes of the communicating implantable devices. The system of claim 1, wherein said one implantable device (10) is provided with programming or intelligent decision means (11-13). The system of claim 2, wherein the or each further implantable device (58; 77; 84) is adapted to be indirectly programmed by said one implantable device (10). The system of any of claims 1 to 3, further comprising at least one further discrete medical device (42; 66) adapted to be provided external to the body, and including means (34, 35; 68, 69) providing bi-directional communication with said one implantable device (10), via a further pair of electrodes (40, 41; 70, 71) of the external device which are adapted to be placed against the external surface of the body, said bi-directional communication comprising the conduction of modulated signals in the frequency range from 10 to 100 kHz through the ion medium of the intra- and extra-cellular body fluids by means of electrolytic-galvanic coupling between the respective pairs of electrodes of the at least one further external device (42; 66) and said one implantable device (10). The system of claim 4, as appendent to claim 2 or claim 3, wherein said one external device (42) is adapted to program said one implantable device (10). The system of any of claims 1 to 5, wherein said one implantable device (10) is is a controllable and/or programmable artificial organ. The system of any of claims 1 to 5, wherein said one implantable device is a cardiac pacemaker (10). The system of claim 7, wherein one said further implantable device is a defibrillator (58). The system of claim 8, wherein said defibrillator (58) includes transmitting means (74) and receiving means (63) for bi-directional communication with said pacemaker (10). The system of any of claims 1 to 9, wherein one said further implantable medical device is a drug delivery device (77). The system of claim 10, wherein said drug delivery device (77) is adapted for bi-directional communication with said one implantable device (10). The system of any of claims 1 to 11, wherein one said further implantable medical device is a sensor (84) for detecting a body parameter including arterial blood pressure, rate of change of blood pressure, temperature, pH value and pO₂ value, and/or a body condition including respiration and body activity. The system of claim 12, wherein said sensor (84) is adapted for bi-directional communication with said one implantable device (10). The system of claim 4 or any claim appendent thereto, wherein one said external medical device is a modem (66) adapted for connection to a telephone circuit. The system of claim 4 or any claim appendent thereto, further comprising an external data recording device (72) coupled to said pair of electrodes (40, 41; 70, 71) of said at least one further external device (42; 66). The system of any of claims 1 to 15, wherein said first and/or second information signal is modulated at 30 kHz. The system of claim 16, wherein said first and/or second information signal has an amplitude from 50 to 500 mV. The system of any of claims 1 to 15, wherein said first and/or second information signal is modulated by frequency-shifting between a pair of frequencies. The system of any of claims 1 to 15, wherein said first and/or second information signal is pulse code modulated. The system of any of claims 1 to 15, wherein said first and/or second information signal is A1 modulated.

Inventors: FUNKE HERMANN D PROF DR MED, FUNKE, HERMANN D., PROF. DR. MED.
Applicants: MEDTRONIC INC, MEDTRONIC, INC.
Application year: 1989
Main classification: A61N1
IPC codes: A61N1, A61M5