Heart stimulation apparatus

Abstract: The invention relates to a heart stimulation apparatus (14) for intracardial stimulation of heart tissue comprising an electrode device (1) with an electrode head (3) provided on the distal end thereof, having at least a first conductive surface (4 - 7) and a second conductive surface (4 - 7), a stimulation pulse generator (21) and a switch (15) for selectively connecting the conductive surface(s) (4 - 7) to the stimulation pulse generator (21) in any possible combination. In order to reduce the energy consumption, an autocapture means (23) is provided which automatically test a number of possible combinations of conductive surfaces (4 - 7) for stimulation and selects the combination providing the lowest stimulation threshold.

Description: This invention relates to a heart stimulation apparatus for intracardial stimulation of heart tissue and/or sensing heart signals in accordance with claim 1. U.S. patent 4,628,934 describes a heart stimulation apparatus in which an electrode device's distal end can be provided with a plurality of independently connectable electrodes. An electrode device is prior art through U.S. patent 3,911,928. A plurality of relatively small conductive surfaces are arrayed on the head of the electrode device in order to reduce the threshold value and, thus, energy consumption. All the conductive surfaces on the head of this electrode device are connected to the same conductor. This can result in needlessly heavy energy consumption, since some of the conductive surfaces are not in contact with hearttissua for stimulation. U.S. patent 4,760,852 describes a pacemaker electrode whose distal end has a plurality of relatively large conductive surfaces connected to the same conductor. US-A-4 848 352 describes an electrode device having a plurality of electrodes which may be combined by electrical connectors to provide a larger electrode. The object of the invention is to achieve a heart stimulation apparatus with which an optimal threshold value for each patient, and therefore the lowest energy consumption is always attained. Another objective is to achieve optimal sensing of heart signals. As a result of this design for the heart stimulation apparatus according to the invention as defined in claim 1, the stimulation surface(s) which provide(s) the lowest stimulation threshold is automatically selected. It is in this connection an advantage if one conductive surface serves as the stimulation electrode, and an other conductive surface(s) serves as indifferent electrode. The autocapture means may test all possible combinations or a selected number of combinations programmed by a physician. Further, the stimulation pulses could also be displaced in time and amplitude at the different surfaces. This means that the duration of pulses could vary, but it also means that a second pulse could arrive before a preceding pulse is emitted. In this manner, a pulse can be given the exact morphology desired. Analogously, the sensing of heart signals can be made from the surface(s) providing the lowest sensing threshold. Another advantageous version of the heart stimulation apparatus is achieved when the number and choice of conductive surfaces, connected via the conductor(s) to the detector for sensing, are selected independently of the conductive surface(s) employed for stimulation. This results In a large selection of sensing surfaces on the electrode head. The sensing surface may be selectable in such a way that it is not the same surface used for stimulation. This would be an advantage in sensing immediately after a stimulation, since the stimulating surface is then polarized, and any sensing could "drown" in the stimulation surface's polarization voltage. According to another embodiment of the invention, it is proposed that the conductive surfaces be evenly distributed over the electrode head. In this way, one or more electrode surface(s) would always be optimally placed against heart tissue. According to an additional embodiment of the invention, it is proposed that the electrode head be hemispherical and that the conductive surfaces be arrayed close to one another. In this manner, a relatively large number of conductive surfaces can be installed on a very small electrode head. The shape of the electrode head ensures that heart tissue is not damaged. According to one preferred embodiment of the invention, the center of the electrode head has a projecting part with a conductive surface. Since the projecting part is extremely small, this part has at least a chance of retaining contact with heart tissue if the electrode head becomes dislocated. Ona version of the invention, simple in design respects, proposes that the electrode head consist of a plurality of conductive bodies which are insulated from one another. With such an embodiment design, the electrode head can have a configuration in which one of the conductive bodies is displaced in relation to the other. The free end of the projecting body, in addition to the sides of the free end, can be insulated to prevent any conduction between the conductive surfaces of the bodies. As a result of the structure of the electrode head, the conductive surfaces of one body or another, can be used for simultaneous stimulation of heart tissue and/or sensing of heart signals. Another embodiment of the invention proposes that the electrode head be equipped with a traumatic fixation component on which at least one conductive surface is provided. This achieves both fixation of the electrode head to the heart wall and ensures that at least two conductive surfaces are in contact with heart tissue. In one constructively simple embodiment of the invention, it is proposed that the fixation component be helical. In this way, the electrode head can be partially screwed into heart tissue. According to one preferred embodiment of the invention, at least one of the conductive surfaces is made of a microporous material. As a result of the microporous material, the stimulation electrode and the indifferent electrode can be made very small while the conductive surfaces are relatively large at the same time. According to an embodiment of the invention, at least one of the conductive surfaces can also be coated with a layer of ion exchange material. The ion exchange material serves e.g. as protection against soiling particles. The conductive surfaces are highly sensitive to such particles, particularly when the surfaces are made from a microporous material. The invention can suitably be refined in an embodiment by having a coating of medication on at least one of the conductive surfaces. This coating has an antlin-flammatory effect when the electrode head presses against or is screwed into the heart wall. In this manner, formation of fibrous tissue around the electrode head, something which otherwise could occur, is avoided or reduced. The invention will be described in greater detail in conjunction with the accompanying drawings, in which FIG. 1 is a side view of a heart stimulation apparatus to which an electrode device according to the invention is connected and shown with an enlarged electrode head, partly in cross-section; FIG. 2 is frontal view of an electrode head according to FIG. 1; FIG. 3 is a cross-section of the electrode device through the section line III-III in FIG. 1; FIG. 4 shows a circuit diagram illustrating the autocapture arrangement in more detail; FIG. 5 illustrates in a flow chart an autocapture routine which the heart stimulation apparatus may perform according to a first test; FIG. 6 illustrates in a flow chart a further autocapture routine which the heart stimulation apparatus may perform, according to a second test. FIG. 1 depicts a heart stimulation apparatus 14 for intracardial stimulation of the heart tissue of a patient and/or sensing heart signals. The apparatus 14 comprises an electrode device 1 containing an electrode cable 2 equipped with a hemispherical electrode head 3 at Its distal end. The electrode head 3 is fitted with four round, closely spaced conductive surfaces 4, 5, 6, 7 which are evenly distributed on the electrode head 3 and which are electrically separated by Insulating material 8. The conductive surface 7 is hidden in this Figure 1. Each conductive surface 4, 5, 6, 7 is connected to its own elongate, flexible conductor 9, 10, 11, 12 extending to the proximal end of the electrode cable, the conductors 9, 10, 11, 12 Insulated from one another. The electrode cable 2 is also provided with an external layer of insulation 13. The heart stimulation apparatus 14 is connected to the proximal end of the electrode cable 2. The heart stimulation apparatus 14 further comprises a switch 15 with four output terminals 16, 17, 18, 19, each connected to its own conductor 9, 10, 11, 12 for the conductive surfaces 4, 5, 6, 7 on the electrode head 3. The switch 15 also has an electronics unit 20 connected to the output terminals 16, 17, 18, 19. The heart stimulation apparatus 14 additionally contains a stimulation pulse generator 21 and a detector 22 for sensing, each of which individually connected to the electronics unit 20, and an autocapture function unit 23 which is connected to the stimulation pulse generator 21, to the detector 22 and to the electronics unit 20. FIG. 2 shows that the conductive surfaces 4, 5, 6, 7 are evenly arrayed on the electrode head 3. The conductive surfaces 4, 5, 6, 7 are the ends of wires made from a conductive material whose other ends are connected to one of the conductors 9, 10, 11, 12, insulated from one another, as shown in cross-section through the electrode device in FIG. 3. After the electrode cable 2 has been introduced into the patient's heart in the known manner and the electrode head is applied to heart tissue, the stimulation generator 21 is switched via the electronics unit 20, e.g. via output terminal 18 and conductor 11, to the conductive surface 6, a voltage for stimulating the heart tissue then being applied to said surface 6. The detector 22 is then switched in the same way, via the electronics unit 20, via one or more of the output terminals 16, 17, 18, 19 and via the corresponding conductor 9, 10, 11, 12, to one or more conductive surfaces 4, 5, 6, 7 for sensing heart signals. The number and selection of conductive surfaces 4, 5, 6, 7 connected to the detector 22, via one or more of the conductors 9, 10, 11, 12, can be selected independently of the conductive surface(s) 4, 5, 6, 7 employed for stimulation. All conductive surfaces 4, 5, 6, 7 can be switched with advantage to the detector 22. In FIG. 4 the structure in the heart stimulation apparatus 14 which executes the autocapture function and selection of electrode surface configuration is shown in a block diagram. The stimulation pulse generator 21, detector 22 and autocapture funciton unit 23 are, as also shown in FIG. 1, connected to the electronics unit 20. In the electronics unit 20 a first switch 121 is connected between output terminal 16 and stimulation pulse generator 21, a second switch 122 is connected between the output terminal 17 and the stimulation pulse generator 21, a third switch 123 is connected between output terminal 18 and the stimulation pulse generator 21, a fourth switch 124 is connected between output terminal 19 and the stimulation pulse generator 21, a fifth switch 125 is connected between output terminal 16 and the detector 22, a sixth switch 126 is connected between output terminal 17 and the detector 22, a seventh switch 127 is connected between output terminal 18 and the detector 22 and an eighth switch 128 is connected between output terminal 19 and the detector 22. The switches 121 - 128 can, when activated by the autocapture function unit 23, selectively connect any output terminal 16, 17, 18, 19 or combination of output terminals 16, 17, 18, 19 to the pulse generator 21 and/or detector 22 respectively. Further, a ninth switch 129 can connect neither, either or both of the stimulation pulse generator 21 and detector 22 to the heart stimulation apparatus's 14 case for unipolar stimutation and sensing. The autocapture function unit 23 is programmed to automatically search for the conductive surface combination which results in the lowest stimulation threshold. This means that the autocapture function unit 23 will selectively, through the switches 121 to 129 test a sequence of different stimulation arrangements and select the most efficient one. The autocapture function in itself Is known. Basically, it is performed by reducing the stimulation energy until there is no reaction from the heart, i.e. no capture, whereafter the stimulation energy is increased until a capture is detected by the detector 22 and the threshold is determined. FIG. 5 illustrates one possible flow chart for performing a selection of the ten lowest thresholds of all programmed combinations. The number of possible combinations could be larger than the number of programmed combinations. This because it may, for instance, not be suitable to stimulate bipolarly between two conductive surfaces which are located too closely to each other. The flow chart commences with the first block by starting TEST A and assign the first combination (n:=1). The function will then proceed with the selection and connection of the first electrode combination, i.e. first combination of conductive surfaces 4, 5, 6, 7, and the threshold is determined for the first combination in a known manner. As this TEST A shall select the ten combinations having the lowest threshold a question block inquires whether the number n has exceeded ten selections. If not, the actual combination and threshold determined will be immediately stored and the number for the actual combination will be incremented by one (n:=n+1). In the next question block it is determined whether all possible combinations N has been tested yet. If so, the test is ended and the ten combinations showing the lowest stimulation threshold will be stored in a memory. If TEST A has not run through all combinations, the next is selected and its threshold determined. When the number of tested combinations exceeds ten (YES in block n>10?), the determined threshold for the actual combination will be compared with the stored thresholds and if any stored threshold is higher than the presently determined threshold (YES in block IS STORED THRESHOLD HIGHER?) the stored combination will be replaced with the present combination and threshold. The number of tested combinations is now incremented and the function proceeds as described above. It should be noted that this flow chart only indicates the carrying out of the autocapture function. If the number of possible combinations is large, it could be vary inconvenient for a patient if the heart stimulation apparatus was to run through all combinations in uninterrupted sequence. In particular the block DETERMINE THRESHOLD could therefore include timing functions reducing the number of tests per hour or the like. When no specific combination has been selected automatically the heart will be stimulated using either a combination and stimulation energy selected by a physician or a combination and stimulation energy previously chosen by the autocapture function. FIG. 6 illustrates a flow chart for a TEST B. TEST B is a continuation of TEST A and in TEST B the stored ten combinations are tested to determine which of the ten that has the lowest threshold. TEST B is routinely performed by the heart stimulation apparatus 14 to ensure that it is the combination having the lowest threshold that is permanently activated. The flow chart begins with a START TEST B block, which could be initiated automatically at selected time intervals by the autocapture function unit 23. The first combination is then addressed (m:=1) and selected in the next block. As in TEST A the threshold Is determined. In TEST B it Is only relevant to find the combination having the lowest threshold and the first threshold will therefore be stored to be compared with other combinations. In the next block the number for the combination is incremented and the function controls if all combinations have been checked yet in which case TEST B is ended. Otherwise the next combination is selected and its threshold determined. The present combination and its threshold is now compared with the stored combination and threshold and if the stored threshold is higher, the present combination and threshold will replace the previously stored combination and threshold and the function proceeds by incrementing the number of combinations. If the stored threshold is lower than the actual threshold the function will only proceed to check out the next combination. When TEST B is ended the autocapture function unit will use the selected combination until a new test may indicate that another number of combination is preferable, or when a physician by telemetry by means of an external programming unit selects a different combination for stimulation. Analogously the autocapture function unit may select a combination of conductive surfaces 4, 5, 6, 7 which provides the best sensing level for the detector 22. It may be convenient if the block DETERMINE THRESHOLD in TEST B, as in TEST A, is provided with means for prolonging the entire test so that the patient will be as unaffected by the TEST as possible. Further, when connected bipolarly the autocapture function unit 23 may switch the connection so that the negative conductive surface(s) becomes positive and vice versa. The pole change may be executed automatically if an increase in the threshold is detected by the autocapture function unit 23, thereby testing which of the two combinations provides the lowest threshold. Conductive surfaces, which are made of a microporous material, can be coated with an ion exchange material and with a layer of medication. The electrode device's electrode head is not limited to the described embodiments. The essential thing is that the conductive surfaces on the electrode head are electrically insulated from one another so the operator has an opportunity to use one or a desired combination of several conductive surfaces for attaining optimal stimulation with minimal energy consumption. The number of conductive surfaces is not limited. In addition, the size and shape of all or some of the surfaces can vary. These embodiments are only limited by the appended claims. REFERENCE LIST 1, Electrode device 2, Electrode cable 3, Electrode head 4, 5, 6, 7, Conductive surface 8 Insulation material 9, 10, 11, 12, Conductor 13. Layer of Insulation 14, Heart stimulation apparatus 15, 121 - 129 Switch 16, 17, 18, 19, Output terminal 20, Electronics unit 21, Stimulation pulse generator 22, Detector 23, Function unit for autocapture

Claims: A heart stimulating apparatus for intracardial stimulation of heart tissue and/or sensing heart signals comprising an electrode device with an electrode head installed on the distal end thereof, whereby the electrode head is equipped with a plurality of conductive surfaces including a first conductive surface (4-7) for stimulating heart tissue and/or sensing heart signals connected to a first conductor (9-12) and at least second and subsequent conducfive surfaces (4-7) for stimulating heart tissue and/or sensing heart signals, said second and subsequent conductive surfaces (4-7) being insulated from the other conductive surfaces (4-7) and each connected to a further conductor (9-12), insulated from the other conductors (9-12), a stimulation pulse generator (21) and a detector (22) and a switch (15) for connecting one of said conductive surfaces (4-7), or a plurality of said conductive surfaces (4-7), to the stimulation pulse generator (21) and/or the detector (22) in any desired manner, wherein the switch is controlled with the aid of an autocapture means in such a way that the conductive surfaces (4-7) are automatically connected in a plurality of different combinations from among all possible combinations via the conductors (9-12), to the stimulation pulse generator (21) and automatically tested according to a first test threshold for stimulation threshold or sensing level wherein said apparatus further comprises means for automatically selecting a predetermined number of said combinations which have the best stimulation threshold or sensing level, said means then automatically testing the selected combinations according to a second test in order to achieve the optimal stimulation with minimal energy consumption or to achieve an optimal sensing level, whereby said second test of said selected combinations is routinely performed to thereby ensure that it is the combination having the optimal threshold which is permanently activated. A heart stimulating apparatus according to claim 1 in which the predetermined number is ten. A heart stimulation apparatus as claimed in any of claims 1 to 2, wherein one conductive surface (4 - 7) serves as the stimulation electrode, and an other conductive surface(s) (4 - 7) serves as the indifferent electrode. A heart stimutation apparatus as claimed in any of claims 1 - 3, wherein the number and choice of conductive surfaces (4 - 7), connected via the conductor(s) (9 - 12) to the detector (22) for sensing, are selected independently of the conductive surface(s) (4 - 7) employed for stimulation. A heart stimulation apparatus as daimed in any of claims 1 - 4, wherein the conductive surfaces (4 - 7) are evenly arrayed on the electrode head (3). A heart stimulation apparatus as claimed in any of claims 1 - 4, wherein the electrode head (3) is hemispherical and the conductive surfaces (4 - 7) are arrayed close to one another. A heart stimulation apparatus as claimed in any of claims 1 - 6, wherein at least one of the conductive surfaces is made of a microporous material. A heart stimulation apparatus as claimed in claim 7, wherein at least one of the conductive surfaces is coated with a layer of an ion exchange material. A heart stimulation apparatus as claimed in claim 8, wherein at least one of the conductive surfaces is coated with a layer of medication.

Inventors: LINDEGREN ULF, LINDEGREN, ULF
Applicants: ST JUDE MEDICAL, ST. JUDE MEDICAL AB
Application year: 1993
Main classification: A61N1
IPC codes: A61N1