Catheter system for defibrillation

Abstract

To provide a catheter system for defibrillation capable of suppressing the time that a user cannot grasp cardiac potential to a short time.SOLUTION: A catheter system 1 for defibrillation includes: a catheter; an electrode part 5 disposed in the catheter; a power source 13 for applying voltage to the electrode part 5; an electro-cardiograph connection part 15; a switching part 30 disposed between the power source 13 and the electro-cardiograph connection part 15 and including one or a plurality of switch elements for switching modes between a defibrillation mode and a potential measuring mode; a first connection line 41A-41D between the switching part 30 and the electro-cardiograph connection part 15; a second connection line 42A-42D between the switching part 30 and the electro-cardiograph connection part 15, the second connecting line 42A to 42D being arranged in parallel with the first connecting line 41A-41D; and a first resistor 51A-51D disposed on the first connection line 41A-41D, which is connected in series with the switching part 30.SELECTED DRAWING: Figure 2

Description

[Technical Field]

[0001] The present invention relates to a defibrillation catheter system used for performing defibrillation in a cardiac chamber. [Background technology]

[0002] Defibrillation is used to treat arrhythmias such as atrial fibrillation and ventricular fibrillation by delivering electrical impulses to restore normal cardiac rhythm. Defibrillation is performed using devices such as automated external defibrillators (AEDs), implantable cardioverter defibrillators (ICDs), defibrillation paddles, and intracardiac defibrillation catheter systems. An intracardiac defibrillation catheter system delivers electrical impulses directly to the heart via electrodes attached to the catheter surface. An intracardiac defibrillation catheter system can also measure intracardiac potentials using the electrodes. Defibrillation catheter systems can use lower-energy voltage waveforms than automated external defibrillators, reducing patient discomfort and allowing them to be used during arrhythmia catheterization and ablation procedures.

[0003] In the treatment of atrial fibrillation, it is necessary to apply a voltage to the heart during the absolute refractory period so that the ventricular muscle does not react. If the heart is stimulated outside the absolute refractory period, the ventricular muscle may react, leading to ventricular fibrillation. For this reason, defibrillation catheter systems apply a voltage in synchronization with the R wave. Patent Document 1 discloses an example of a defibrillation catheter system. [Prior art documents] [Patent documents]

[0004] [Patent Document 1] Japanese Patent Application Laid-Open No. 2010-220778 Summary of the Invention [Problem to be solved by the invention]

[0005] In defibrillation procedures, from a safety perspective, it is desirable to constantly display cardiac potential data measured by a catheter on the electrocardiograph screen except when defibrillation voltage is being applied. In the intracardiac defibrillation catheter system described in Patent Document 1, the electrocardiograph screen display is temporarily turned off in defibrillation mode, where the contact of the switching unit switches to the second contact. The contact of the switching unit then switches to the first contact, returning the system to the cardiac potential measurement mode. However, when the system returns to the cardiac potential measurement mode, even though the potential data measured by the electrode unit has been input to the electrocardiograph, the potential data may not be displayed on the electrocardiograph screen for approximately 10 to 20 seconds. In other words, even when defibrillation voltage is not being applied, there may be a long period of time during which the user is unable to grasp the cardiac potential. Therefore, an object of the present invention is to provide a defibrillation catheter system that can shorten the period during which the user is unable to grasp the cardiac potential. [Means for solving the problem]

[0006] A defibrillation catheter system according to an embodiment of the present invention that can solve the above problems is as follows. [1] A catheter having a longitudinal axis; an electrode portion disposed at a distal portion of the catheter; a power source that applies a voltage to the electrode portion; an electrocardiograph connection unit connected to an electrocardiograph; a switching unit including one or more switch elements arranged between the power source and the electrocardiograph connection unit, and configured to switch between a defibrillation mode in which a voltage is applied to the electrode unit and a potential measurement mode in which a potential is measured by the electrode unit; a first connection line between the switching unit and the electrocardiograph connection unit; a second connection line between the switching unit and the electrocardiograph connection unit, the second connection line being arranged in parallel with the first connection line; a first resistor disposed on the first connection line and connected in series with the switching unit.

[0007] Furthermore, the defibrillation catheter system according to the embodiment is preferably any one of the following [2] to

[11] . [2] The device further includes a control unit connected to the switching unit and configured to switch between the defibrillation mode and the potential measurement mode, The defibrillation catheter system according to [1], wherein the control unit controls the switch element of the switching unit so that the switching unit is connected to the first connection line in the defibrillation mode and the switching unit is connected to the second connection line in the potential measurement mode. [3] The switching unit has a one-circuit two-contact switch, a common contact of the one-pole two-contact switch connected to the power supply; a first contact of the single-pole, two-contact switch connected to the first resistor; A defibrillation catheter system according to [1] or [2], wherein the second contact of the one-pole, two-contact switch is connected to the electrocardiograph connection section without a resistor. [4] The defibrillation catheter system further includes a second resistor disposed on the second connection line and having a resistance value smaller than that of the first resistor; The switching unit has a one-circuit two-contact switch, a common contact of the one-pole two-contact switch connected to the power supply; a first contact of the single-pole, two-contact switch connected to the first resistor; The defibrillation catheter system according to [1] or [2], wherein the second contact of the one-pole, two-contact switch is connected to the second resistor. [5] The switching unit has a first on / off switch connected to the first connection line and a second on / off switch connected to the second connection line, the first on-off switch is connected to the first resistor; The defibrillation catheter system according to [1] or [2], wherein the second on / off switch is connected to the electrocardiograph connection section without a resistor. [6] The defibrillation catheter system further includes a second resistor disposed in the second connection line and connected in series with at least one of the one or more switches included in the switching unit, the second resistor having a resistance value smaller than that of the first resistor; the switching unit has a first on / off switch connected to the first connection line and a second on / off switch connected to the second connection line, the first on-off switch is connected to the first resistor; The defibrillation catheter system according to [1] or [2], wherein the second on / off switch is connected to the second resistor. [7] One end of the first connection line is connected to the switching unit, one end of the second connection line is connected to the switching unit, the other end of the first connection line and the other end of the second connection line are connected to each other at a connection portion, The defibrillation catheter system according to any one of [3] to [6], further comprising a third connection line between the connection part and the electrocardiograph connection part, and a third resistor arranged on the third connection line and having a resistance value smaller than that of the first resistor. [8] The defibrillation catheter system according to any one of [1] to [6], wherein the resistance value of the first resistor is 10 kΩ or more and 10 MΩ or less. [9] The defibrillation catheter system according to [4] or [6], wherein the resistance value of the second resistor is 50Ω or more and 150Ω or less.

[10] The defibrillation catheter system according to [7], wherein the resistance value of the third resistor is 50Ω or more and 150Ω or less.

[11] The defibrillation catheter system according to [3] or [4], wherein the switching unit further includes a power supply side on / off switch arranged closer to the power supply than the one-circuit two-contact switch.

[12] The defibrillation catheter system described in [5] or [6], wherein the switching unit further includes a power supply side on / off switch arranged on the power supply side of the first on / off switch and on the power supply side of the second on / off switch. [Effects of the Invention]

[0008] According to the defibrillation catheter system, when defibrillation is performed, the switching unit and the first resistor can be controlled to be connected to the first connection line, which is arranged in series, thereby preventing high voltage from being applied to the electrocardiograph during defibrillation. Furthermore, because the connection between the electrocardiograph and the catheter system is maintained by the first connection line even in defibrillation mode, the measured potential at the electrode unit can be quickly restored when returning to potential measurement mode after defibrillation. This stabilizes the baseline of the electrocardiograph, speeds up recovery of the electrocardiograph screen display, and shortens the time the user cannot grasp the cardiac potential. [Brief explanation of the drawings]

[0009] [Figure 1] 1 is a schematic diagram of a defibrillation catheter system according to one embodiment of the present invention. FIG. [Figure 2] FIG. 1 is a circuit diagram showing a state of a defibrillation mode in a defibrillation catheter system according to an embodiment of the present invention. [Figure 3] FIG. 3 is a circuit diagram showing the state of a potential measurement mode in the defibrillation catheter system shown in FIG. 2. [Figure 4] FIG. 3 is a circuit diagram showing a modification of the defibrillation catheter system shown in FIG. 2. [Figure 5] FIG. 3 is a circuit diagram showing another modified example of the defibrillation catheter system shown in FIG. 2. [Figure 6] FIG. 10 is a circuit diagram showing yet another modified example of the defibrillation catheter system shown in FIG. 2. [Figure 7] FIG. 10 is a circuit diagram showing yet another modified example of the defibrillation catheter system shown in FIG. 2. [Figure 8]FIG. 10 is a circuit diagram showing yet another modified example of the defibrillation catheter system shown in FIG. 2. [Figure 9] FIG. 10 is a circuit diagram showing yet another modified example of the defibrillation catheter system shown in FIG. 2. [Figure 10] FIG. 10 is a circuit diagram showing yet another modified example of the defibrillation catheter system shown in FIG. 2. DETAILED DESCRIPTION OF THE INVENTION

[0010] The present invention will be described in more detail below based on the following embodiments. However, the present invention is not limited to the following embodiments, and can be implemented with appropriate modifications within the scope of the above and below-described purposes, and all such modifications are included within the technical scope of the present invention. For convenience, hatching and component symbols may be omitted in the drawings. In such cases, reference should be made to the specification or other drawings. The dimensions of various components in the drawings may differ from actual dimensions, as priority is given to helping understand the features of the present invention.

[0011] A defibrillation catheter system according to one embodiment of the present invention comprises a catheter having a longitudinal axis, an electrode disposed at a distal portion of the catheter, a power source for applying a voltage to the electrode, an electrocardiograph connection portion connected to an electrocardiograph, a switching portion disposed between the power source and the electrocardiograph connection portion and including one or more switch elements for switching between a defibrillation mode in which a voltage is applied to the electrode and a potential measurement mode in which a potential is measured by the electrode, a first connection line between the switching portion and the electrocardiograph connection portion, a second connection line between the switching portion and the electrocardiograph connection portion and the second connection line is disposed in parallel with the first connection line, and a first resistor disposed on the first connection line and connected in series with the switching portion. According to the defibrillation catheter system, when defibrillation is performed, the switching portion and the first resistor can be controlled to be connected to the first connection line disposed in series, thereby preventing a high voltage from being applied to the electrocardiograph during defibrillation. Furthermore, because the connection between the electrocardiograph and the catheter system is maintained by the first connection line even in defibrillation mode, the measured potential at the electrode unit can be restored quickly when returning to potential measurement mode after defibrillation. This stabilizes the baseline of the electrocardiograph, speeds up recovery of the electrocardiograph screen display, and shortens the time the user cannot grasp the cardiac potential.

[0012] A defibrillation catheter system according to an embodiment of the present invention will be described with reference to FIGS. 1 to 10. FIG. 1 is a schematic diagram of a defibrillation catheter system according to an embodiment of the present invention. FIG. 2 is a circuit diagram showing a defibrillation mode state in a defibrillation catheter system according to an embodiment of the present invention. FIG. 3 is a circuit diagram showing a potential measurement mode state in the defibrillation catheter system shown in FIG. 2. FIGS. 4 to 10 are circuit diagrams showing modifications of the defibrillation catheter system shown in FIG. 2. Hereinafter, the defibrillation catheter system may be simply referred to as a system. As shown in FIGS. 1 and 2, system 1 includes a catheter 2, an electrode unit 5, a power source 13, an electrocardiograph connection unit 15, a switching unit 30, a first connection line, a second connection line, and a first resistor. 1 and 2, system 1 includes an electrical defibrillation device 10, which may include an electrode unit 5, a power source 13, an electrocardiograph connection unit 15, a switching unit 30, a first connection line, a second connection line, and a first resistor. Hereinafter, the electrical defibrillation device may be simply referred to as the electrical device.

[0013] As can be seen from FIG. 1, the catheter 2 has a longitudinal direction. The longitudinal direction refers to the direction from the proximal side to the distal side of the catheter 2. The proximal side of the catheter 2 refers to the side closer to the user (operator) in the direction in which the catheter 2 extends, and the distal side refers to the side opposite the proximal side (i.e., the side to be treated). The catheter 2 preferably has a circumferential direction and a radial direction. As shown in FIG. 1, an electrode unit 5 is disposed in the distal portion of the catheter 2. The electrode unit 5 is preferably composed of two or more electrodes, and it is more preferable that the electrode unit 5 has at least one pair of a positive electrode and a negative electrode.

[0014] By inserting the catheter 2 into a cardiac cavity and bringing the electrode unit 5 into contact with the inner surface of the atrium, ventricle, or blood vessel, the electrode unit 5 detects minute voltages generated in association with cardiac pulsation, thereby measuring the intracardiac potential. As will be described later, an electrocardiogram waveform (also referred to as electrocardiogram waveform or electrocardiogram data) can be obtained using an electrocardiograph 70 or the like based on the measured electrocardiogram signal. Therefore, the electrocardiogram signal measured by the electrode unit 5 is preferably input to the input unit 22, which will be described later. The electrocardiogram signal measured by the electrode unit 5 is preferably taken into the electrocardiograph 70.

[0015] The catheter 2 is inserted into a cardiac cavity, the electrode unit 5 is brought into contact with the inner surface of the atrium, ventricle, or blood vessel, and a voltage is applied to the electrode unit 5, thereby providing an electrical stimulus to the heart. For example, a voltage can be applied so that a current flows from the positive electrode through the living body to the negative electrode, or from the negative electrode through the living body to the positive electrode.

[0016] The catheter 2 may be a cylindrical resin tube. The resin tube may be manufactured by extrusion molding, for example. The resin tube may have one or more lumens. The catheter 2 may be made of a single layer or multiple layers. A portion of the catheter 2 in the longitudinal or circumferential direction may be made of a single layer, and the other portion may be made of multiple layers.

[0017] Examples of resins that can be used to form the catheter 2 include polyamide resins, polyester resins, polyurethane resins, polyolefin resins, fluorine resins, vinyl chloride resins, silicone resins, and natural rubber. These resins can be used alone or in combination of two or more. Among these, polyamide resins, polyester resins, polyurethane resins, polyolefin resins, and fluorine resins are preferred.

[0018] The electrode unit 5 preferably has a plurality of electrodes. The plurality of electrodes are preferably arranged at positions offset in the longitudinal direction of the catheter 2. This allows intracardiac potentials to be measured at various positions. For example, by measuring the potential difference between adjacent electrodes, the intracardiac potentials between the electrodes can be measured. For example, as shown in FIGS. 1 and 2, the electrode unit 5 may have a first electrode group 6 including a first most distal electrode 6A and a first most proximal electrode 6B, and a second electrode group 7 including a second most distal electrode 7A and a second most proximal electrode 7B. The second electrode group 7 is preferably located more proximal than the first electrode group 6 in the longitudinal direction of the catheter 2. In other words, the second electrode group 7 is located closer to the proximal end of the first most proximal electrode 6B, which is located most proximal in the first electrode group 6. It is preferable that the distal end of the second most distal electrode 7A, which is located most distal among the first and second electrode groups, is located on the proximal side. As such, it is preferable that the first electrode group 6 and the second electrode group 7 each have multiple electrodes. This allows voltage to be applied to a wide area of ​​the heart, thereby enabling efficient defibrillation. It is preferable that the first electrode group 6 is located at a position corresponding to the coronary sinus, and the second electrode group 7 is located at a position corresponding to the right atrium. FIG. 1 shows an example in which the first electrode group 6 has eight electrodes and the second electrode group 7 has eight electrodes.

[0019] The electrode in the first electrode group 6 may be a positive electrode or a negative electrode. When the electrode in the first electrode group 6 is a positive electrode, the electrode in the second electrode group 7 may be a negative electrode. When the electrode in the first electrode group 6 is a negative electrode, the electrode in the second electrode group 7 may be a positive electrode.

[0020] It is preferable that DC voltages of different polarities are applied to the multiple electrodes of the electrode unit 5. Specifically, it is preferable that DC voltages of different polarities are applied to the electrodes of the first electrode group 6 and the electrodes of the second electrode group 7. Current can be applied from the electrodes of the first electrode group 6 to the electrodes of the second electrode group 7, or vice versa. The current waveform may be monophasic, in which the polarity is constant, but is preferably biphasic, in which the polarity is reversed midway. A biphasic waveform can eliminate defibrillation with less energy. The current energy applied to the living body can be set, for example, to between 1 J and 30 J.

[0021] It is preferable that a voltage of the same polarity (positive or negative) is applied to each of the multiple electrodes in the first electrode group 6. It is also preferable that a voltage of the same polarity (negative or positive) is applied to each of the multiple electrodes in the second electrode group 7. For example, when applying a biphasic DC voltage, a current can be passed from the right atrium toward the coronary sinus by applying a negative voltage to the electrodes in the first electrode group 6 and a positive voltage to the electrodes in the second electrode group 7 in the first half of the current application, and a current can be passed from the coronary sinus toward the right atrium by applying a positive voltage to the electrodes in the first electrode group 6 and a negative voltage to the electrodes in the second electrode group 7 in the second half of the current application.

[0022] The number of electrodes in the first electrode group 6 and the number of electrodes in the second electrode group 7 may be different, but are preferably the same. Having these numbers the same makes it easy to make the total surface area of ​​the electrodes in the first electrode group 6 and the total surface area of ​​the electrodes in the second electrode group 7 the same. By evenly arranging the same number of electrodes and making the total surface area of ​​the electrodes in the first electrode group 6 and the total surface area of ​​the electrodes in the second electrode group 7 the same, it is possible to improve the accuracy of measuring intracardiac potentials and perform defibrillation efficiently.

[0023] The number of electrodes in the first electrode group 6 and the number of electrodes in the second electrode group 7 are each, for example, preferably 6 or more, more preferably 8 or more, and preferably 12 or less, more preferably 10 or less.

[0024] When the first electrode group 6 has multiple electrodes, it is preferable that the separation distance between adjacent electrodes in the first electrode group 6 in the longitudinal axis direction is shorter than the separation distance between the first most proximal electrode 6B of the first electrode group 6 and the second most distal electrode 7A of the second electrode group 7.

[0025] When the second electrode group 7 has multiple electrodes, it is preferable that the separation distance between adjacent electrodes in the second electrode group 7 in the longitudinal axis direction is shorter than the separation distance between the first most proximal electrode 6B of the first electrode group 6 and the second most distal electrode 7A of the second electrode group 7.

[0026] The electrode unit 5 is preferably connected to the electrocardiograph 70. The electrode unit 5 is preferably connected to the electrocardiograph 70 via the defibrillation electrical device 10. One or more electrodes in the first electrode group 6 and one or more electrodes in the second electrode group 7 are preferably connected to the electrocardiograph 70.

[0027] The electrode unit 5 may have one or more electrodes located more proximal than the second electrode group 7. By arranging the electrodes in this manner, it is possible to measure the intracardiac potential over a wider range. For example, in FIG. 1, the electrode unit 5 has a third electrode group 8 including multiple electrodes located more proximal than the second electrode group 7. In FIG. 1, the third electrode group 8 has four electrodes. It is preferable that the third electrode group 8 be electrodes dedicated to measuring the intracardiac potential, and it is preferable that no voltage is applied by the third electrode group 8.

[0028] The third electrode group 8 is preferably connected to the electrocardiograph 70. Although Fig. 2 shows only electrodes 8A-8B of the third electrode group 8, it is preferable that the other electrodes are also connected to the electrocardiograph 70. The third electrode group 8 and the electrocardiograph 70 may be connected via a switch element or a resistor, but as shown in Fig. 2, they are preferably connected without a switch element or a resistor. By connecting the third electrode group 8 and the electrocardiograph 70 without a switch element or a resistor, the intracardiac potential can be measured with high accuracy.

[0029] The surface areas of the electrodes of the electrode unit 5 may be different from one another, but are preferably the same. By making the surface areas the same, the measurement accuracy of the intracardiac potential can be improved.

[0030] In the electrode section 5, the widths of the multiple electrodes in the longitudinal direction of the catheter 2 may be different, but are preferably the same. By making the electrode widths the same, the measurement accuracy of the intracardiac potential can be improved. The width of each electrode is preferably, for example, 0.5 mm or more and 5 mm or less.

[0031] In the electrode section 5, the spacing between adjacent electrodes in the longitudinal direction of the catheter 2, i.e., the distance between the distal end of one electrode and the proximal end of the other electrode located distal to the first electrode, is preferably, for example, 1 mm to 10 mm, more preferably 3 mm to 8 mm. Setting the spacing in this manner can improve the accuracy of measuring intracardiac potentials.

[0032] Each electrode of the electrode unit 5 is preferably present in an area covering more than half of the outer circumference of the catheter 2, and more preferably in an area covering the entire outer circumference of the catheter 2. Each electrode of the electrode unit 5 is more preferably ring-shaped. Such an electrode shape increases the contact area with the heart, making it easier to measure intracardiac potentials and apply electrical stimulation.

[0033] The electrodes of the electrode unit 5 preferably contain a conductive material such as platinum or stainless steel, and among conductive materials, they more preferably contain a radiopaque material, and even more preferably contain an X-ray opaque material. Of these, it is preferable that each electrode contains platinum. When the electrodes contain a radiopaque material, the position of the electrodes can be easily determined under radioscopy.

[0034] A conductor (lead wire) is connected to each electrode of the electrode unit 5. For example, one end of the conductor disposed in the lumen of the resin tube constituting the catheter 2 is joined to the inner circumferential surface of the electrode through a side hole provided in the outer circumferential surface of the resin tube. The other end of the conductor is preferably connected to a predetermined connector of the defibrillation electrical device 10 described below.

[0035] A distal tip 3 is preferably provided at the distal end of the catheter 2. The distal tip 3 preferably has a portion whose outer diameter decreases toward the distal end of the distal tip 3. This can improve the ease of insertion of the catheter 2 into the body.

[0036] Examples of materials that can be used to form the distal tip 3 include conductive materials and polymeric materials. In particular, the distal tip 3 can function as an electrode when it is made of a conductive material. The hardness of the distal tip 3 is preferably lower than that of the catheter 2. This allows the distal tip 3 to protect body tissue when it comes into contact with a body cavity.

[0037] A handle 4 is preferably provided on the proximal side of the catheter 2, which is held by the user when operating the catheter 2. The size of the handle 4 is not particularly limited as long as it is suitable for holding with one hand. The length of the handle 4 is not particularly limited, but is preferably, for example, 5 cm or more and 20 cm or less. The outermost diameter (circular equivalent diameter) of the handle 4 is not particularly limited, but is preferably, for example, 1 cm or more and 5 cm or less. The handle 4 can be made of a material such as a synthetic resin, such as ABS or polycarbonate, or a foamed plastic, such as polyurethane foam.

[0038] As shown in FIGS. 1 and 2, the system 1 has a power supply 13 that applies a voltage to the electrode unit 5. The power supply 13 preferably has one or more capacitors. The power supply 13 preferably has a power supply circuit for generating a DC voltage. The power supply circuit may have, for example, a boost circuit that boosts the DC voltage and one or more capacitors that charge the applied voltage. For example, it is preferable that a charging switch 63, which is preferably provided, is turned on, so that a predetermined applied voltage is applied to the capacitor and the capacitor is charged. In FIG. 2, the power supply 13 is connected to a signal generating unit 21 and a switching unit 30. The power supply 13 is preferably connected to the switching unit 30 via a power waveform switching unit 24, which will be described later.

[0039] The system 1 may have a component connection section for connecting the defibrillation electrical device 10 to a component other than the defibrillation electrical device 10, such as an electrocardiograph 70. For example, as shown in FIG. 2, the system 1 has an electrocardiograph connection section 15 connected to the electrocardiograph 70. It is more preferable that the electrocardiograph connection section 15 be provided in the defibrillation electrical device 10. In FIG. 2, the switching section 30 and the electrocardiograph 70 are connected via the electrocardiograph connection section 15. Also, in FIG. 2, the electrocardiograph 70 and the switching section 30 are connected via at least one of the first resistor, the second resistor, and the third resistor and a conductor, but it is also possible to replace some or all of the wired connection with a wireless connection.

[0040] The system 1 may further include a member connection section connected to the electrode section 5 of the catheter 20. For example, as shown in FIG. 2, the system 1 may include an electrode connection section 16 connected to the electrode section 5. The electrode connection section 16 is preferably connected to the electrodes of the first electrode group 6 and the electrodes of the second electrode group 7. The system 1 may also include a second electrocardiograph connection section 17 connected to the electrocardiograph 70 and a second electrode connection section 18 connected to the electrodes of the third electrode group 8. In FIG. 2, within the defibrillation electrical device 10, the electrocardiograph connection section 15 and the electrode connection section 16 are connected via a switching section 30, at least one of the first resistor, the second resistor, and the third resistor, and a conductor, and the second electrocardiograph connection section 17 and the second electrode connection section 18 are connected to each other via a conductor.

[0041] The electrocardiograph connection portion 15, the electrode connection portion 16, the second electrocardiograph connection portion 17, and the second electrode connection portion 18 are preferably terminals for connection, and for example, connectors can be used. Examples of connectors include a concave connector and a convex connector. These may be part of the circuit constituting the control portion 20, or may be terminals physically connected to the conductors connected to the electrocardiograph 70 or the electrode portion 5, or may be part of a wireless communication device that receives electrocardiographic signals. Furthermore, when connecting components together, wired connections using conductors can be partially or entirely replaced with wireless connections.

[0042] The system 1 is disposed between the power source 13 and the electrocardiograph connection unit 15 and has a switching unit 30 including one or more switch elements for switching between a defibrillation mode (FIG. 2) in which a voltage is applied to the electrode unit 5 and a potential measurement mode (FIG. 3) in which a potential is measured by the electrode unit 5. In the defibrillation mode, the power source 13 and the electrode unit 5 are electrically connected. In the potential measurement mode, the power source 13 and the electrode unit 5 are electrically disconnected. The switching unit 30 preferably switches from the defibrillation mode to the potential measurement mode and from the potential measurement mode to the defibrillation mode. The switching unit 30 preferably switches modes based on an electrocardiogram signal input from an input unit 22, which will be described later.

[0043] The system 1 has a first connection line between the switching unit 30 and the electrocardiograph connection unit 15, a second connection line between the switching unit 30 and the electrocardiograph connection unit 15, the second connection line being arranged in parallel to the first connection line, and a first resistor arranged on the first connection line and connected in series to the switching unit 30. For example, in FIGS. 2 and 3, the system 1 has first connection lines 41A to 41D and second connection lines 42A to 42D arranged in parallel with the first connection lines 41A to 41D, respectively, and a first resistor 51A is arranged on the first connection line 41A, a first resistor 51B is arranged on the first connection line 41B, a first resistor 51C is arranged on the first connection line 41C, and a first resistor 51D is arranged on the first connection line 41D. According to system 1, when defibrillation is performed, control can be performed so that switching unit 30 and first resistors 51A-51D are connected to first connection lines 41A-41D arranged in series, thereby preventing high voltage from being applied to the electrocardiograph during defibrillation. Furthermore, because the connection between electrocardiograph 70 and system 1 is maintained by first connection lines 41A-41D even in defibrillation mode, the measured potential at electrode unit 5 can be quickly restored when returning to potential measurement mode after defibrillation. This stabilizes the baseline of electrocardiograph 70, quickly restores the screen display of electrocardiograph 70, and shortens the time during which the user is unable to grasp the cardiac potential.

[0044] In this specification, the connection lines are used to transmit electrical signals between the switching unit 30 and the electrocardiograph connection unit 15, and are made of conductive materials such as conductors or connectors. The first connection line 41 and the second connection line 42 are each located in part or all of the path between the switching unit 30 and the electrocardiograph connection unit 15. In Figs. 2 and 3, one end of each of the first connection lines 41A to 41D is directly connected to the switching unit 30, and one end of each of the second connection lines 42A to 42D is directly connected to the switching unit 30. The other end of each of the first connection lines 41A to 41D and the other end of each of the second connection lines 42A to 42D are directly connected to each other by connection parts 43A to 43D.

[0045] 2 and 3, the system 1 may have third connection lines 45A to 45D between the connection parts 43A to 43D that connect the wiring and the electrocardiograph connection part 15. One end of the third connection lines 45A to 45D may be directly connected to the connection parts 43A to 43D, and the other end of the third connection lines 45A to 45D may be directly connected to the electrocardiograph connection part 15. An electrical path from the switching part 30 to the electrocardiograph connection part 15 may be formed by the first connection lines 41A to 41D, the second connection lines 42A to 42D, and the third connection lines 45A to 45D. Although not shown, the system 1 does not necessarily have to include the third connection lines 45A to 45D. For example, one end of each of the first connection lines 41A to 41D may be directly connected to the switching unit 30, and the other end may be directly connected to the electrocardiograph connection unit 15, and one end of each of the second connection lines 42A to 42D may be directly connected to the switching unit 30, and the other end of each of the second connection lines 42A to 42D may be directly connected to the electrocardiograph connection unit 15. Here, direct connection includes a mode in which conductors are directly connected to each other, and a mode in which connectors arranged at the ends of conductors are connected to each other.

[0046] The first resistors 51A to 51D are protective resistors that prevent high voltage from being applied to the electrocardiograph during defibrillation. The first resistors 51A to 51D are resistors, and do not include resistances included in other electric elements or wiring on the first connection lines 41A to 41D.

[0047] The resistance values ​​of the first resistors 51A-51D need only be large enough to protect the electrocardiograph when a voltage is applied from the power supply 13 to the electrode unit 5 in the defibrillation mode. The resistance values ​​of the first resistors 51A-51D are preferably 10 kΩ or more, more preferably 30 kΩ or more, and even more preferably 50 kΩ or more, and are preferably 10 MΩ or less, more preferably 5 MΩ or less, and even more preferably 1 MΩ or less. Setting the resistance values ​​in this manner ensures that the electrocardiograph is protected.

[0048] It is preferable that one first connection line, one second connection line, and one first resistor are provided for each electrode of the electrode unit 5. It is more preferable that one first connection line, one second connection line, and one first resistor are provided for each electrode of the first electrode group 6 and each electrode of the second electrode group 7. In FIGS. 2 and 3, for electrode 6A, a first connection line 41A is provided between the one-circuit two-contact switch 32A and the electrocardiograph connection unit 15, a second connection line 42A is provided between the one-circuit two-contact switch 32A and the electrocardiograph connection unit 15, and a first resistor 51A is provided on the first connection line 41A. Similarly, for electrodes 6B, 7A, and 7B, first connection lines 41B to 41D are arranged between the one-circuit two-contact switches 32B to 31D and the electrocardiograph connection unit 15, second connection lines 42B to 42D that are parallel to the first connection lines 41B to 41D are arranged between the one-circuit two-contact switches 32B to 31D and the electrocardiograph connection unit 15, and first resistors 51B to 51D are arranged on the first connection line 41B, respectively.

[0049] As shown in FIG. 2, the first resistor is connected in series with the switching unit 30, and is preferably connected in series with the one-circuit two-contact switch.

[0050] When the switching unit 30 has a one-circuit, two-contact switch, it is preferable that the common contact of the one-circuit, two-contact switch is connected to the power supply 13, the first contact of the one-circuit, two-contact switch is connected to the first resistor, and the second contact of the one-circuit, two-contact switch is connected to the electrocardiograph connection unit 15 without a resistor. For example, in FIGS. 2 and 3 , for electrode 6A, the common contact of one-circuit, two-contact switch 32A is connected to the power supply 13, the first contact of one-circuit, two-contact switch 32A is connected to the first resistor 51A, and the second contact of one-circuit, two-contact switch 32A is connected to the electrocardiograph connection unit 15 without a resistor. Similarly, for electrodes 6B, 7A, and 7B, the common contact of switches 32B to 32D is connected to the power supply 13, the first contacts of switches 32B to 32D are connected to first resistors 51B to 51D, respectively, and the second contacts of switches 32B to 32D are connected to the electrocardiograph 15 without a resistor. Since the switching unit 30 has such one-circuit two-contact switches 32A to 32D, mode switching can be performed in a short time, and the measured potential at the electrode unit 5 can be restored quickly when returning to the potential measurement mode after defibrillation. Furthermore, since the second contact is connected to the electrocardiograph connection unit 15 without via a resistor, loss of the electrical signal obtained at the electrode unit 5 can be minimized, and more accurate intracardiac potential data can be easily transmitted from the electrode unit 5 to the electrocardiograph 70 when the second contact is selected.

[0051] As shown in Fig. 2, in the defibrillation mode, the first contacts of the one-circuit two-contact switches 32A to 32D are preferably selected, and in the potential measurement mode, as shown in Fig. 3, the second contacts of the one-circuit two-contact switches 32A to 32D are preferably selected. When the first contacts of the switches 32A to 32D are selected, electrical energy from the power source 13 is supplied to the electrode unit 5, and the measured potential obtained at the electrode unit 5 is preferably input to the electrocardiograph 70 via the first resistors 51A to 51D on the first connection lines 41A to 41D. When the second contacts are selected, the measured potential obtained at the electrode unit 5 is preferably input to the electrocardiograph 70 via the second connection lines 42A to 42D.

[0052] 2 and 3 show an example in which the switching section 30 has an electrocardiograph-side switch section 31, and the electrocardiograph-side switch section 31 has four one-circuit two-contact switches 32A to 32D.

[0053] It is preferable that a one-pole, two-contact switch is provided for each electrode in the electrode unit 5. It is more preferable that one one-pole, two-contact switch is provided for each of the electrodes in the first electrode group 6 and the second electrode group 7. By providing one-pole, two-contact switches, it is possible to individually control the application of voltage to each electrode. In FIGS. 2 and 3, switch 32A is connected to electrode 6A, switch 32B is connected to electrode 6B, switch 32C is connected to electrode 7A, and switch 32D is connected to electrode 7B.

[0054] It is preferable that the multiple one-pole, two-contact switches included in the electrocardiograph-side switch section 31 are independent from one another. By being independent from one another, the electrodes included in the first electrode group 6 and the electrodes included in the second electrode group 7 can be electrically separated, and each electrode can be controlled independently.

[0055] As shown in FIGS. 2 and 3, it is preferable that the plurality of one-circuit two-contact switches included in the electrocardiograph-side switch section 31 are connected in parallel.

[0056] Although not shown, instead of a one-circuit, two-contact switch connected to each electrode to which a voltage is applied, the switching unit 30 may have a multi-pole, double-throw switch. The number of poles of the multi-pole, double-throw switch is preferably the same as the total number of electrodes in the first electrode group 6 and the second electrode group.

[0057] The switches of the switching unit 30 refer to switching elements mounted on the electronic circuit board, and are distinguished from operational switches such as push button switches and lever switches that are operated by the user to switch on and off. By appropriately combining the contacts and on / off states of the switches of the switching unit 30, it is possible to apply voltage and measure intracardiac potentials by outputting DC voltage from the power supply 13 to each electrode. The same applies to the following explanation.

[0058] A relay switch or a semiconductor switch can be used as the switch element of the electrocardiograph-side switch unit 31. Examples of semiconductor switch elements include IGBT, MOSFET, thyristor, an element using a SiC semiconductor, and an element using a GaN semiconductor.

[0059] Although different types of switches may be used as the multiple switch elements included in the electrocardiograph-side switch section 31, it is preferable to use the same type of switches. By using the same type of switches, the control of the system 1 can be simplified.

[0060] 2 and 3 show an example in which resistors are not provided on the second connection lines 42A-42D, but resistors may be provided on the second connection lines 42A-42D. For example, as shown in Fig. 4, the defibrillation catheter system 1 may further include second resistors 52A-52D arranged on the second connection lines 42A-42D and having a resistance value smaller than that of the first resistors 51A-51D. In this case, it is preferable that the switching unit 30 includes one-circuit two-contact switches 32A-32D, the common contact of the one-circuit two-contact switches 32A-32D is connected to the power source 13, the first contacts of the one-circuit two-contact switches 32A-32D are connected to the first resistors 51A-51D, and the second contacts of the one-circuit two-contact switches 32A-32D are connected to the second resistors 52A-52D. Even if the second contact is selected and the measured potential obtained at the electrode unit 5 is input to the electrocardiograph 70 via the second resistors 52A to 52D on the second connection lines 42A to 42D, accurate intracardiac potential data can be transmitted from the electrode unit 5 to the electrocardiograph 70 because the resistance values ​​of the second resistors 52A to 52D are smaller than the resistance values ​​of the first resistors 51A to 51D.

[0061] 4, a second resistor 52A is arranged on the second connection line 42A, a second resistor 52B is arranged on the second connection line 42B, a second resistor 52C is arranged on the second connection line 42C, and a second resistor 52D is arranged on the second connection line 42D. A first contact of the switch 32A is connected to the first resistor 51A, and a second contact of the switch 32B is connected to the first resistor 51B, and a second contact of the switch 32B is connected to the second resistor 52B. A first contact of the switch 32C is connected to the first resistor 51C, and a second contact of the switch 32C is connected to the second resistor 52C. A first contact of the switch D is connected to the first resistor 51D, and a second contact of the switch D is connected to the second resistor 52D.

[0062] The intracardiac potential data measured by the electrode unit 5 is a weak electrical signal of about 1 to 10 mV, but by providing the second resistors 52A to 52D on the second connection lines 42A to 42D, the current flowing through the second connection lines 42A to 42D can be adjusted, making it easier to protect the electrical signal from noise and improving the stability of the circuit.

[0063] The second resistors 52A to 52D are resistors, and the second resistors 52A to 52D do not include resistances included in other electric elements or wiring on the second connection lines 42A to 42D.

[0064] The second resistor has a smaller resistance value than the first resistor, meaning that the resistance value of the second resistor connected to the second contact of one one-circuit, two-contact switch should be smaller than the resistance value of the first resistor connected to the first contact of the switch. Note that it is preferable that the resistance value of each of the second resistors is smaller than the resistance values ​​of all of the first resistors in the system 1.

[0065] The resistance values ​​of the second resistors 52A to 52D need only be large enough to appropriately adjust the currents flowing through the second connection lines 42A to 42D. The resistance values ​​of the second resistors 52A to 52D are preferably 50Ω or more, more preferably 60Ω or more, and even more preferably 80Ω or more, and are preferably 150Ω or less, more preferably 130Ω or less, and even more preferably 110Ω or less. Setting the resistance values ​​in this manner can improve the stability of the circuit.

[0066] 4, it is preferable that the first contact be selected in the defibrillation mode and the second contact be selected in the potential measurement mode. When the first contact is selected, electrical energy from the power source 13 is supplied to the electrode unit 5, and the measured potential obtained at the electrode unit 5 is preferably input to the electrocardiograph 70 via the first resistors 51A-51D on the first connection lines 41A-41D. When the second contact is selected, it is preferable that the measured potential obtained at the electrode unit 5 is input to the electrocardiograph 70 via the second resistors 52A-52D on the second connection lines 42A-42D.

[0067] It is preferable that a second resistor is provided for each electrode in the electrode unit 5. It is more preferable that one second resistor is provided for each of the electrodes in the first electrode group 6 and the electrodes in the second electrode group 7.

[0068] 2, the second resistors 52A to 52D are connected in series with the switching unit 30, and are preferably connected in series with the one-circuit two-contact switch. The second resistors 52A to 52D are preferably arranged in parallel with the first resistors 51A to 51D, respectively.

[0069] For other configurations of the system shown in FIG. 4, the explanations of the configurations shown in FIGS. 2 and 3 can be referred to as appropriate.

[0070] 2 to 3 and 5, in a case where one end of each of the first connection lines 41A to 41D is connected to the switching unit 30, one end of each of the second connection lines 42A to 42D is connected to the switching unit 30, and the other end of each of the first connection lines 41A to 41D and the other end of each of the second connection lines 42A to 42D are connected to each other via the connecting units 43A to 43D, the defibrillation catheter system 1 may further include third connection lines 45A to 45D between the connecting units 43A to 43D and the electrocardiograph connecting unit 15, and third resistors 53A to 53D arranged on the third connection lines 45A to 45D and having a resistance value smaller than that of the first resistors 51A to 51D. In detail, in Figure 5, the other end of the first connection line 41A and the other end of the second connection line 42A are connected at connection part 43A, the other end of the first connection line 41B and the other end of the second connection line 42B are connected at connection part 43B, the other end of the first connection line 41C and the other end of the second connection line 42C are connected at connection part 43C, and the other end of the first connection line 41D and the other end of the second connection line 42D are connected at connection part 43D. In addition, in Figure 5, the system 1 further includes a third connection line 45A between the connection portion 43A and the electrocardiograph connection portion 15, a third connection line 45B between the connection portion 43B and the electrocardiograph connection portion 15, a third connection line 45C between the connection portion 43C and the electrocardiograph connection portion 15, a third connection line 45D between the connection portion 43D and the electrocardiograph connection portion 15, a third resistor 53A having a smaller resistance value than the first resistor 51A, a third resistor 53B having a smaller resistance value than the first resistor 51B, a third resistor 53C having a smaller resistance value than the first resistor 51C, and a third resistor 53D having a smaller resistance value than the first resistor 51D.By providing the third resistors 53A to 53D on the third connection lines 45A to 45D, similar to the second resistor, even if the second contact is selected and the measured potential obtained at the electrode unit 5 is input to the electrocardiograph 70 via the second connection lines 42A to 42D and the third resistors 53A to 53D on the third connection lines 45A to 45D, accurate intracardiac potential data can be transmitted from the electrode unit 5 to the electrocardiograph 70 because the resistance value of the third resistors 53A to 53D is smaller than the resistance value of the first resistors 51A to 51D.

[0071] The third resistors 53A to 53D are resistors, and the third resistors 53A to 53D do not include resistors included in other electric elements or wiring on the third connection lines 45A to 45D.

[0072] The third resistor has a smaller resistance value than the first resistor, meaning that the resistance value of the third resistor connected to one one-circuit, two-contact switch should be smaller than the resistance value of the first resistor connected to the first contact of the switch. Note that it is preferable that the resistance value of each of the third resistors is smaller than the resistance values ​​of all of the first resistors in the system 1.

[0073] The resistance values ​​of the third resistors 53A to 53D need only be large enough to appropriately adjust the currents flowing through the third connection lines 45A to 45D. The resistance values ​​of the third resistors 53A to 53D are preferably 50Ω or more, more preferably 60Ω or more, and even more preferably 80Ω or more, and are preferably 150Ω or less, more preferably 130Ω or less, and even more preferably 110Ω or less. Setting the resistance values ​​in this manner can improve the stability of the circuit.

[0074] 5, it is preferable that the first contact be selected in the defibrillation mode and the second contact be selected in the potential measurement mode. When the first contact is selected, electrical energy from the power source 13 is supplied to the electrode unit 5, and the measured potential obtained at the electrode unit 5 is preferably input to the electrocardiograph 70 via the first resistors 51A-51D on the first connection lines 41A-41D and the third resistors 53A-53D on the third connection lines 45A-45D. When the second contact is selected, it is preferable that the measured potential obtained at the electrode unit 5 is input to the electrocardiograph 70 via the second connection lines 42A-42D and then the third resistors 53A-53D on the third connection lines 45A-45D.

[0075] It is preferable that a third resistor is provided for each electrode in the electrode unit 5. It is more preferable that one third resistor is provided for each of the electrodes in the first electrode group 6 and the electrodes in the second electrode group 7.

[0076] 5, the third resistors 53A to 53D are preferably connected in series with the one-circuit two-contact switches 32A to 32D, and the third resistors 53A to 53D are preferably connected in series with the first resistors 51A to 51D, respectively.

[0077] For other configurations of the system shown in FIG. 5, the explanations of the configurations shown in FIGS. 2 to 4 can be referred to as appropriate.

[0078] 6, the switching unit 30 has one-circuit two-contact switches 32A to 32D, a common contact of the one-circuit two-contact switches 32A to 32D is connected to the power source 13, first contacts of the one-circuit two-contact switches 32A to 32D are connected to the first resistors 51A to 51D, second contacts of the one-circuit two-contact switches 32A to 32D are connected to the second resistors 52A to 52D, one ends of the first connection lines 41A to 41D are connected to the switching unit 30, and the second connection lines 42A to 42D are connected to the first resistors 51A to 51D. When one end of each of the first connection lines 41A-41D and the other end of each of the second connection lines 42A-42D are connected to the switching unit 30, and the other end of each of the first connection lines 41A-41D and the other end of each of the second connection lines 42A-42D are connected to each other by the connection parts 43A-43D, the system 1 may further include third connection lines 45A-45D between the connection parts 43A-43D and the electrocardiograph connection unit 15, and third resistors 53A-53D arranged on the third connection lines 45A-45D and having a resistance value smaller than that of the first resistors 51A-51D. By providing the first resistors 51A-51D, second resistors 52A-52D, and third resistors 53A-53D in this manner, accurate intracardiac potential data can be transmitted from the electrode unit 5 to the electrocardiograph 70. In detail, even if the second contact is selected and the measured potential obtained at the electrode unit 5 is input to the electrocardiograph 70 via the second resistors 52A to 52D on the second connection lines 42A to 42D and the third resistors 53A to 53D on the third connection lines 45A to 45D, accurate intracardiac potential data can be transmitted from the electrode unit 5 to the electrocardiograph 70 because the resistance values ​​of the second resistors 52A to 52D and the third resistors 53A to 53D are each smaller than the resistance values ​​of the first resistors 51A to 51D.

[0079] For other configurations of the system shown in FIG. 6, the explanations of the configurations shown in FIGS. 2 to 5 can be referred to as appropriate.

[0080] 2 and 3, switching unit 30 preferably further includes power-side on / off switches 36A-36D that are arranged closer to the power source than one-circuit, two-contact switches 32A-32D. Specifically, in FIGS. 2 and 3, power-side on / off switch 36A is arranged for electrode 6A, and switch 36A is connected to switch 32A. Power-side on / off switch 36B is arranged for electrode 6B, and switch 36B is connected to switch 32B. Power-side on / off switch 36C is arranged for electrode 7A, and switch 36C is connected to switch 32C. Power-side on / off switch 36D is arranged for electrode 7B, and switch 36D is connected to switch 32D. By including power-side on / off switches 36A-36D in switching unit 30, voltage application and intracardiac potential measurement can be performed by appropriately combining the on / off of these switches with the switching of the contacts of one-circuit, two-contact switches 32A-32D. Note that being arranged on the power supply side means that the power supply side on / off switches 36A to 36D are arranged closer to the power supply 13 than the one-circuit two-contact switches 32A to 32D.

[0081] It is preferable that the one-circuit two-contact switches 32A to 32D and the power-side on / off switches 36A to 36D are independent of each other in the switching unit 30. By being independent of each other, the electrodes of the first electrode group 6 and the electrodes of the second electrode group 7 can be electrically separated, and each electrode can be controlled independently.

[0082] It is preferable that a power supply on / off switch is provided for each electrode in the electrode unit 5. It is more preferable that one power supply on / off switch is provided for each of the electrodes in the first electrode group 6 and the second electrode group 7. By providing the power supply on / off switches, it is possible to individually control the application of voltage to each electrode.

[0083] It is preferable that the multiple power supply-side on / off switches are independent of each other. This allows the electrodes in the first electrode group 6 and the electrodes in the second electrode group 7 to be electrically separated, allowing each electrode to be controlled independently.

[0084] As shown in FIGS. 2 and 3, it is preferable that the plurality of power supply side on / off switches are connected in parallel.

[0085] Although not shown, instead of a power supply on / off switch connected to each electrode to which a voltage is applied, the switching unit 30 may have a multi-pole double-throw switch. The number of poles of the multi-pole double-throw switch is preferably the same as the total number of electrodes in the first electrode group 6 and the second electrode group.

[0086] Examples of switch elements used in the power supply side on / off switch include relay switches and semiconductor switches, such as IGBTs, MOSFETs, thyristors, elements using SiC semiconductors, and elements using GaN semiconductors.

[0087] The power supply-side on / off switches may be of different types, but it is preferable to use the same type of switches, as this simplifies the control of the system 1.

[0088] 2 and 3 show an example in which the switching unit 30 has one-circuit, two-contact switches 32A-32D, but on-off switches may be provided instead of the one-circuit, two-contact switches. For example, as shown in Fig. 7, the switching unit 30 may have first on-off switches 33A-33D connected to first connection lines 41A-41D and second on-off switches 34A-34D connected to second connection lines 42A-42D, the first on-off switches 33A-33D may be connected to first resistors 51A-51D, and the second on-off switches 34A-34D may be connected to the electrocardiograph connection unit 15 without via resistors. 7, for electrode 6A, switching unit 30 has a first on / off switch 33A connected to first connection line 41A and a second on / off switch 34A connected to second connection line 42A, with first on / off switch 33A connected to first resistor 51A and second on / off switch 34A connected to electrocardiograph connection unit 15 without a resistor. For electrode 6B, switching unit 30 has a first on / off switch 33B connected to first connection line 41B and a second on / off switch 34B connected to second connection line 42B, with first on / off switch 33B connected to first resistor 51B and second on / off switch 34B connected to electrocardiograph connection unit 15 without a resistor. For electrode 7A, switching unit 30 has a first on / off switch 33C connected to first connection line 41C and a second on / off switch 34C connected to second connection line 42C, with first on / off switch 33C connected to first resistor 51C and second on / off switch 34C connected to electrocardiograph connection unit 15 without a resistor. For electrode 7B, switching unit 30 has a first on / off switch 33D connected to first connection line 41D and a second on / off switch 34D connected to second connection line 42D, with first on / off switch 33D connected to first resistor 51D and second on / off switch 34D connected to electrocardiograph connection unit 15 without a resistor.By providing an on / off switch on each of the first and second connection lines in this way, mode switching can be performed in a short time, and the measured potential at the electrode unit 5 can be restored quickly when returning to the potential measurement mode after defibrillation. Furthermore, since the second on / off switch is connected to the electrocardiograph connection unit 15 without a resistor, loss of the electrical signal obtained at the electrode unit 5 can be minimized, and when the second on / off switch is turned on, more accurate intracardiac potential data can be transmitted from the electrode unit 5 to the electrocardiograph 70 via the second connection line.

[0089] 2-3 and 7, in the defibrillation mode, it is preferable that the first on-off switches 33A-33D are on and the second on-off switches 34A-34D are off, and in the potential measurement mode, it is preferable that the first on-off switches 33A-33D are off and the second on-off switches 34A-34D are on. When the first on-off switches 33A-33D are on and the second on-off switches 34A-34D are off, electrical energy from the power source 13 is supplied to the electrode unit 5, and the measured potential obtained at the electrode unit 5 is preferably input to the electrocardiograph 70 via the first resistors 51A-51D on the first connection lines 41A-41D. When the first on-off switches 33A-33D are off and the second on-off switches 34A-34D are on, it is preferable that the measured potential obtained at the electrode unit 5 is input to the electrocardiograph 70 via the second connection lines 42A-42D.

[0090] FIG. 7 shows an example in which the switching section 30 has an electrocardiograph-side switch section 31, and the electrocardiograph-side switch section 31 has four first on-off switches 33A to 33D and four second on-off switches 34A to 34D.

[0091] It is preferable that one first on / off switch and one second on / off switch are provided for each electrode in the electrode unit 5. It is more preferable that one first on / off switch and one second on / off switch are provided for each electrode in the first electrode group 6 and each electrode in the second electrode group 7. By providing the switches in this way, it is possible to individually control the application of voltage to each electrode.

[0092] It is preferable that the multiple on / off switches included in the electrocardiograph-side switch unit 31 are independent from one another. By being independent from one another, the electrodes included in the first electrode group 6 and the electrodes included in the second electrode group 7 can be electrically separated, and each electrode can be controlled independently.

[0093] As shown in FIG. 7, it is preferable that the plurality of on / off switches included in the electrocardiograph-side switch section 31 are connected in parallel.

[0094] A relay switch or a semiconductor switch can be used as the switch element of the on / off switch of the electrocardiograph-side switch unit 31. Examples of semiconductor switch elements include IGBT, MOSFET, thyristor, an element using a SiC semiconductor, and an element using a GaN semiconductor.

[0095] The plurality of on / off switches included in the electrocardiograph-side switch section 31 may use different types of switch elements, but it is preferable to use the same type of switch elements.

[0096] For other configurations of the system shown in FIG. 7, the explanations of the configurations shown in FIGS. 2 to 5 can be referred to as appropriate.

[0097] FIG. 4 shows an example in which the switching unit 30 has one-circuit two-contact switches 32A to 32D and second resistors 52A to 52D are provided on the second connection lines 42A to 42D, but on-off switches may be provided instead of the one-circuit two-contact switches. For example, as shown in FIG. 8, the defibrillation catheter system 1 may further include second resistors 52A-52D arranged in the second connection lines 42A-42D and connected in series with at least one of the one or more switches included in the switching unit 30, the second resistors 52A-52D having a resistance value smaller than that of the first resistors 51A-51D, and the switching unit 30 may include first on-off switches 33A-33D connected to the first connection lines 41A-41D and second on-off switches 34A-34D connected to the second connection lines 42A-42D, with the first on-off switches 33A-33D connected to the first resistors 51A-51D and the second on-off switches 34A-34D connected to the second resistors 52A-52D. 8, second on-off switch 34A is connected to second resistor 52A, second on-off switch 34B is connected to second resistor 52B, second on-off switch 34C is connected to second resistor 52C, and second on-off switch 34D is connected to second resistor 52D. Even if first on-off switches 33A-33D are off and second on-off switches 34A-34D are on and the measured potential obtained at electrode unit 5 is input to electrocardiograph 70 via second resistors 52A-52D on second connection lines 42A-42D, accurate intracardiac potential data can be transmitted from electrode unit 5 to electrocardiograph 70 because the resistance values ​​of second resistors 52A-52D are smaller than the resistance values ​​of first resistors 51A-51D.

[0098] 2-3 and 8, in the defibrillation mode, it is preferable that the first on-off switches 33A-33D are on and the second on-off switches 34A-34D are off, and in the potential measurement mode, it is preferable that the first on-off switches 33A-33D are off and the second on-off switches 34A-34D are on. When the first on-off switches 33A-33D are on and the second on-off switches 34A-34D are off, electrical energy from the power supply 13 is supplied to the electrode unit 5, and the measured potential obtained at the electrode unit 5 is input to the electrocardiograph 70 via the first resistors 51A-51D on the first connection lines 41A-41D. When the first on / off switches 33A to 33D are off and the second on / off switches 34A to 34D are on, the measured potential obtained at the electrode unit 5 is preferably input to the electrocardiograph 70 via the second resistors 52A to 52D on the second connection lines 42A to 42D.

[0099] For other configurations of the system shown in FIG. 8, the explanations of the configurations shown in FIGS. 2 to 7 can be referred to as appropriate.

[0100] FIG. 5 shows an example in which the switching unit 30 has one-circuit two-contact switches 32A to 32D and third resistors 53A to 53D are provided on the third connection lines 45A to 45D, but on-off switches may be provided instead of the one-circuit two-contact switches. For example, as shown in FIG. 9, when the switching unit 30 has first on / off switches 33A to 33D connected to the first connection lines 41A to 41D and second on / off switches 34A to 34D connected to the second connection lines 42A to 42D, one end of the first connection lines 41A to 41D is connected to the switching unit 30, one end of the second connection lines 42A to 42D is connected to the switching unit 30, and the other end of the first connection lines 41A to 41D and the other end of the second connection lines 42A to 42D are connected to each other by connection parts 43A to 43D, the defibrillation catheter system 1 may further have third connection lines 45A to 45D between the connection parts 43A to 43D and the electrocardiograph connection unit 15, and third resistors 53A to 53D arranged on the third connection lines 45A to 45D and having a resistance value smaller than that of the first resistors 51A to 51D. By providing the third resistors 53A to 53D on the third connection lines 45A to 45D, similar to the second resistors, even if the first on / off switches 33A to 33D are turned off and the second on / off switches 34A to 34D are turned on and the measured potential obtained at the electrode unit 5 is input to the electrocardiograph 70 via the second connection lines 42A to 42D and the third resistors 53A to 53D on the third connection lines 45A to 45D, accurate intracardiac potential data can be transmitted from the electrode unit 5 to the electrocardiograph 70 because the resistance value of the third resistors 53A to 53D is smaller than the resistance value of the first resistors 51A to 51D.

[0101] 2-3 and 9, in the defibrillation mode, it is preferable that the first on-off switches 33A-33D are on and the second on-off switches 34A-34D are off, and in the potential measurement mode, it is preferable that the first on-off switches 33A-33D are off and the second on-off switches 34A-34D are on. When the first on-off switches 33A-33D are on and the second on-off switches 34A-34D are off, electrical energy from the power source 13 is supplied to the electrode unit 5, and the measured potential obtained at the electrode unit 5 is input to the electrocardiograph 70 via the first resistors 51A-51D on the first connection lines 41A-41D and the third resistors 53A-53D on the third connection lines 45A-45D. When the first on / off switches 33A to 33D are off and the second on / off switches 34A to 34D are on, the measured potential obtained at the electrode section 5 is preferably input to the electrocardiograph 70 via the second connection lines 42A to 42D and then via the third resistors 53A to 53D on the third connection lines 45A to 45D.

[0102] For other configurations of the system shown in FIG. 9, the explanations of the configurations shown in FIGS. 2 to 8 can be referred to as appropriate.

[0103] 10, the switching unit 30 has first on / off switches 33A to 33D connected to the first connection lines 41A to 41D and second on / off switches 34A to 34D connected to the second connection lines 42A to 42D, one ends of the first connection lines 41A to 41D are connected to the switching unit 30, one ends of the second connection lines 42A to 42D are connected to the switching unit 30, and the other ends of the first connection lines 41A to 41D and the other ends of the second connection lines 42A to 42D are connected to each other. When the electrodes 5 are connected by the connection units 43A-43D, the first on-off switches 33A-33D are connected to first resistors 51A-51D, the second on-off switches 34A-34D are connected to second resistors 52A-52D, and the system 1 may further include third connection lines 45A-45D between the connection units 43A-43D and the electrocardiograph connection unit 15, and third resistors 53A-53D arranged on the third connection lines 45A-45D and having a resistance value smaller than that of the first resistors 51A-51D. By providing the first resistors 51A-51D, second resistors 52A-52D, and third resistors 53A-53D in this manner, accurate intracardiac potential data can be transmitted from the electrode unit 5 to the electrocardiograph 70. Even if the first on / off switches 33A to 33D are turned off and the second on / off switches 34A to 34D are turned on and the measured potential obtained at the electrode unit 5 is input to the electrocardiograph 70 via the second resistors 52A to 52D on the second connection lines 42A to 42D and the third resistors 53A to 53D on the third connection lines 45A to 45D, accurate intracardiac potential data can be transmitted from the electrode unit 5 to the electrocardiograph 70 because the resistance values ​​of the second resistors 52A to 52D and the third resistors 53A to 53D are each smaller than the resistance values ​​of the first resistors 51A to 51D.

[0104] For other configurations of the system shown in FIG. 10, the explanations of the configurations shown in FIGS. 2 to 9 can be referred to as appropriate.

[0105] 2-3 and 7-9, a power supply-side on / off switch may also be provided in a configuration in which the switching unit has a first on / off switch and a second on / off switch. For example, the switching unit 30 may further include power supply-side on / off switches 36A-36D that are arranged closer to the power supply 13 than the first on / off switches 33A-33D and closer to the power supply 13 than the second on / off switches 34A-34D. By including the power supply-side on / off switches 36A-36D in the switching unit 30, appropriate combinations of the on / off of these switches and the on / off of the first on / off switches 33A-33D and the second on / off switches 34A-34D can be used to apply a voltage and measure an intracardiac potential by outputting a DC voltage from the power supply 13 to each electrode.

[0106] For the configuration of the power supply side on / off switch, the explanation of the configuration shown in FIGS. 2 to 5 can be referred to as appropriate.

[0107] 2, the system 1 further includes a control unit 20 connected to the switching unit 30 and configured to switch between a defibrillation mode and a potential measurement mode. The control unit 20 preferably controls the switch elements of the switching unit 30 so that the switching unit 30 is connected to the first connection lines 41A to 41D in the defibrillation mode and the second connection lines 42A to 42D in the potential measurement mode. Since the control unit 20 can control each switch element of the switching unit 30, a DC voltage from the power source 13 can be output to each electrode, enabling defibrillation by voltage application. It is more preferable that the control unit 20 be connected to each switch element of the switching unit 30.

[0108] The control unit 20 is preferably connected to an input unit 22, which will be described later. This allows the control unit 20 to control the on / off switching of each switch element connected to the control unit 20 based on the electrocardiogram signal input from the input unit 22.

[0109] To avoid complicating the drawing, in FIG. 2, the control unit 20 is connected to the switching unit 30, but it is preferable that the control unit 20 is connected to each switch that the switching unit 30 has.

[0110] As shown in FIG. 2, the system 1 preferably includes a signal generating unit 21 that generates a signal that permits application of a voltage to the electrode unit 5. The permitting signal is not particularly limited as long as it is a signal related to the application of a voltage for defibrillation, and examples thereof include a signal that permits charging the power source 13, a signal that permits generation of a pulse voltage, a signal that permits voltage application, and a signal that permits switching on or off each switch element. The signal generating unit 21 may generate at least one of these permitting signals. In another embodiment, some of these permitting signals may be generated by operating the operating unit, etc.

[0111] The signal generating unit 21 is preferably connected directly or indirectly to the power supply 13 .

[0112] The signal generating unit 21 may be connected to the control unit 20 or may be provided within the control unit 20 .

[0113] 2 and 3, in system 1, a power supply waveform switching unit 24 is preferably provided in the connection path between power supply 13 and power supply-side on / off switches 36A to 36D. Power supply waveform switching unit 24 can output the voltage input from power supply 13 as pulsed power. By switching the polarity with power supply waveform switching unit 24, the polarity of the outputs from first electrode group 6 and second electrode group 7 can be inverted.

[0114] Power supply waveform switching unit 24 has waveform switches 24A-24B, and is preferably controlled so that after power supply-side on / off switches 36A-36D are turned on, waveform switches 24A-24B are turned from off to on, and then power supply 13 applies a voltage to electrode unit 5. By turning waveform switches 24A-24B from off to on, a DC voltage from power supply 13 is output to the electrodes via waveform switches 24A-24B. This provides power supply 13 with a fail-safe function that can prevent voltage from being unintentionally applied to a patient when, for example, power supply-side on / off switches 36A-36D fail.

[0115] Power supply waveform switching unit 24 may be provided with only one waveform switch or with multiple waveform switches. When system 1 has multiple power supply on / off switches and multiple waveform switches, one waveform switch may be connected to each power supply on / off switch. In Figures 2 and 3, waveform switch 24A is connected to power supply on / off switches 36A and 36B so as to correspond to electrodes 6A and 6B, and waveform switch 24B is connected to power supply on / off switches 36C and 36D so as to correspond to electrodes 7A and 7B.

[0116] The number of waveform switches is not particularly limited, but it is preferable that at least one is provided for the anode side of power supply 13 and at least one is provided for the cathode side of electrode 13. Furthermore, at least one waveform switch may be provided for each electrode in first electrode group 6, and at least one may be provided for each electrode in second electrode group 7.

[0117] The waveform changeover switch may be, for example, a relay switch or a semiconductor switch. Examples of semiconductor switch elements include IGBT, MOSFET, thyristor, elements using SiC semiconductor, and elements using GaN semiconductor.

[0118] The waveform changeover switch may be of a single-pole single-throw type or a multi-pole single-throw type, but is preferably of a multi-pole single-throw type.

[0119] In order to reduce errors in the voltages applied to the multiple electrodes, the system 1 may have a wiring connection unit 9 that connects the wiring of the multiple electrodes together. The wiring connection unit 9 may have a first wiring connection unit that connects the wiring connected to each of the multiple electrodes in the first electrode group 6 to each other. This shorts the wiring connected to the first electrode group 6 to each other. For the same reason, the wiring connection unit 9 may have a second wiring connection unit that connects the wiring connected to each of the multiple electrodes in the second electrode group 7 to each other.

[0120] The system 1 preferably has one or more operation units for performing various operations such as turning the electric device 10 on and off, setting the amount of applied energy, charging voltage, applying voltage, selecting application electrodes, etc. Known input means such as a push button switch or a lever can be used as the operation unit.

[0121] The system 1 may have a main power switch 61 for turning on and off the main power of the electrical device 10. Examples of the main power switch 61 include a push button switch, a slide switch, and a rocker switch. When the main power switch 61 is turned on, an intracardiac potential may be measured by the electrode unit 5 of the catheter 2. When the main power switch 61 is turned on, the system may enter a cardiac potential measurement mode.

[0122] The system 1 may have an applied energy setting switch 62 for setting the amount of applied energy. Examples of the applied energy setting switch 62 include a touch panel, a dial switch, and a push button switch.

[0123] The system 1 may have a charging switch 63 for instructing the start of energy charging. Examples of the charging switch 63 include a touch panel and a push button switch. When the charging switch 63 is turned on, it is preferable that the signal generating unit 21 generates a signal to instruct the power source 13 to start charging with energy. Then, it is preferable that charging of the capacitor 14 that the power source 13 preferably has starts upon receiving the signal from the signal generating unit 21.

[0124] System 1 may have an application execution switch 64 for instructing the start of voltage application. Examples of application execution switch 64 include a touch panel and a push button switch. When application execution switch 64 is turned on, signal generating unit 21 preferably generates a signal permitting the application of voltage for defibrillation. This allows the user to operate application execution switch 64 and apply voltage at the user's timing.

[0125] The system 1 may have an electrode selection switch 65 for selecting an electrode to which the voltage is to be applied. Examples of the electrode selection switch 65 include a touch panel and a push button switch.

[0126] At least one of the main power switch 61, the applied energy setting switch 62, the charging switch 63, the application execution switch 64, and the electrode selection switch 65 is preferably connected to the switching unit 30. At least one of the main power switch 61, the applied energy setting switch 62, the charging switch 63, the application execution switch 64, and the electrode selection switch 65 is preferably connected to the power source 13. At least one of the main power switch 61, the applied energy setting switch 62, the charging switch 63, the application execution switch 64, and the electrode selection switch 65 is preferably connected to the control unit 20. As a result, input signals from the various operation switches are transmitted to the control unit 20. At least one of the main power switch 61, the applied energy setting switch 62, the charging switch 63, the application execution switch 64, and the electrode selection switch 65 is preferably provided in the electrical device 10.

[0127] 2, an impedance measuring unit 25 may be disposed in the connection path between the power supply 13 and the switching unit 30. The impedance measuring unit 25 preferably measures the impedance between the two electrodes of the electrode unit 5, or between the first electrode group 6 and the second electrode group 7. By measuring the impedance, it is possible to set an applied waveform suited to the patient.

[0128] It is preferable that, after the impedance measurement by the impedance measurement unit 25 is completed, the power supply 13 is controlled to apply a voltage to the electrode unit 5. For example, after the application execution switch 64 is turned on, the following may be performed in order: generation of an enable signal from the signal generation unit 21, switching of the switches in the switching unit 30, measurement of the impedance by the impedance measurement unit 25, and application of a voltage to the electrode unit 5 by the power supply 13.

[0129] After the charging switch 63 is turned on, the impedance measurement unit 25 may start measuring the impedance. That is, the impedance measurement may start and / or end before the application execution switch 64 is turned on.

[0130] 1 to 3, the system 1 is preferably connected to an electrocardiograph 70. The electrocardiograph 70 is a device that creates an electrocardiogram waveform (electrocardiogram waveform) based on an electrocardiogram signal (also called an electrocardiogram signal or ECG signal) that measures potential changes that occur between electrodes inserted into the heart, between electrodes attached to the body surface, or between an electrode inserted into the heart and an electrode attached to the body surface. The vertical axis of the electrocardiogram waveform represents potential (e.g., in mV), and the horizontal axis represents time (e.g., in seconds).

[0131] The electrocardiograph 70 may have an amplifier circuit that amplifies the electrocardiographic signal measured by the electrodes. The amplifier circuit may be, for example, a differential amplifier circuit. In the electrocardiograph 70, a filter circuit may be connected to the amplifier circuit. The filter circuit may perform processing such as removing noise and baseline fluctuations from the signal amplified by the amplifier circuit. The filter circuit may be connected downstream of the amplifier circuit. The electrocardiograph 70 may have an analog-to-digital conversion circuit (AD conversion circuit) that converts analog signals to digital signals. The AD conversion circuit may be connected downstream of the amplifier circuit or the filter circuit. The electrocardiograph 70 may have a display unit for displaying electrocardiographic waveforms. Examples of the display unit include a liquid crystal display. While known electrocardiographs 70 can be used, it is preferable that the electrocardiograph 70 creates electrocardiographic waveforms based on intracardiac potentials measured by the electrode unit 5 of the catheter 2. The system 1 may have a display device provided separately from the electrocardiograph 70. Examples of the display device include a computer, an external monitor, a mobile phone, a smartphone, and a tablet terminal.

[0132] The electrocardiograph 70 may be connected to the power supply 13. For example, the electrocardiograph 70 may be connected to the defibrillation electrical device 10 including the power supply 13. When the electrocardiograph 70 is connected to the power supply 13, it is preferable that an overvoltage protection circuit that protects the electrocardiograph 70 from overvoltage is provided in the connection path between the power supply 13 and the electrocardiograph 70. By providing an overvoltage protection circuit, it is possible to prevent damage to the electrocardiograph 70 due to application of an overvoltage to the electrocardiograph 70. An overvoltage protection circuit is a circuit that has the function of suppressing overvoltage and providing protection when an input or output becomes overvoltage due to an external surge voltage, a device abnormality, or the like.

[0133] For example, as shown in FIGS. 1 to 3, the system 1 preferably includes an input unit 22 to which an electrocardiographic signal is input and which is connected to an electrocardiograph 70. This allows each switch element to be controlled to switch from a cardiac potential measurement mode to a defibrillation mode or vice versa based on the electrocardiographic signal. The defibrillation electrical device 10 included in the system 1 preferably includes the input unit 22. The input unit 22 is preferably disposed in the control unit 20. The input unit 22 may be part of a circuit constituting the control unit 20, an input terminal physically connected to a device that measures the electrocardiographic signal, or part of a wireless communication device that receives the electrocardiographic signal. The electrocardiographic signal input to the input unit 22 may be obtained based on an intracardiac potential measured by electrodes inserted into the heart, or may be obtained based on a body surface potential measured by electrodes attached to the body surface.

[0134] As shown in FIGS. 2 and 3 , the system 1 preferably includes an R-wave detection unit 23 connected to the input unit 22 and configured to detect R-waves using the electrocardiographic signal input to the input unit 22. In the treatment of atrial fibrillation, voltage must be applied to the heart during the absolute refractory period to prevent ventricular muscle reaction. Therefore, voltage application is generally synchronized with R-waves. Therefore, detecting R-waves with the R-wave detection unit 23 can prevent stimulation of the heart outside the absolute refractory period. The R-wave detection unit 23 is preferably disposed in the control unit 20. The R-wave detection unit 23 may be part of a circuit constituting the control unit 20, an input terminal physically connected to a device that measures the electrocardiographic signal, or part of a wireless communication device that receives the electrocardiographic signal. The defibrillation electrical device 10 included in the system 1 preferably includes the R-wave detection unit 23. The R-wave detection unit 23 preferably detects the peak of an R-wave from the electrocardiographic signal. Furthermore, the R-wave detection unit 23 preferably detects at least one of the peaks of a P wave and a Q wave from the electrocardiographic signal.

[0135] At least one of the functions of the system 1, for example, the functions of the control unit 20, the signal generating unit 21, the input unit 22, the R-wave detecting unit 23, the power supply waveform switching unit 24, and the impedance measuring unit 25, may be realized by hardware or software. Examples of hardware include logic circuits formed in integrated circuits such as LSI (Large Scale Integration) and ASIC (Application Specific Integrated Circuit).

[0136] The system 1 may include a computer that executes instructions of a program, which is software for realizing at least one function of the control unit 20, the signal generating unit 21, the input unit 22, the R-wave detecting unit 23, the power supply waveform switching unit 24, and the impedance measuring unit 25. The computer preferably includes a processor and a computer-readable recording medium storing the program. The processor executes the program stored in the computer-readable recording medium to realize the above functions. A CPU (Central Processing Unit) can be used as the processor. A ROM (Read Only Memory) or the like can be used as the recording medium. The recording medium can also include a RAM (Random Access Memory). The program can be supplied to the computer via any transmission medium capable of transmitting the program. Examples of the transmission medium include a communication network and a communication line. [Explanation of symbols]

[0137] 1: Defibrillation catheter system 2: Catheter 3: Tip 4: Handle 5: Electrode part 10:Electrical device for defibrillation 13: Power supply 15: Electrocardiograph connection part 20: Control unit 21: Signal generator 22: Input section 23: R wave detection unit 24: Power waveform switching section 24A~24B: Waveform switch 25: Impedance measurement section 30: Switching section 32A~32D: 1-circuit 2-contact switch 33A~33D: First on / off switch 34A~34D: Second on / off switch 36A~36D: Power supply on / off switch 41A to 41D: First connection line 42A~42D: Second connection line 43: Connection 45A~45D: Third connection line 51A~51D: 1st resistor 52A~52D: Second resistor 53A~53D: Third Resistor 61: Main power switch 62: Applied energy setting switch 63: Charging switch 64: Apply execution switch 65: Electrode selection switch 70:Electrocardiograph

Claims

1. a catheter having a longitudinal axis; an electrode portion disposed at a distal portion of the catheter; a power source that applies a voltage to the electrode portion; an electrocardiograph connection unit connected to an electrocardiograph; a switching unit including one or more switch elements arranged between the power source and the electrocardiograph connection unit, and configured to switch between a defibrillation mode in which a voltage is applied to the electrode unit and a potential measurement mode in which a potential is measured by the electrode unit; a first connection line between the switching unit and the electrocardiograph connection unit; a second connection line between the switching unit and the electrocardiograph connection unit, the second connection line being arranged in parallel with the first connection line; a first resistor disposed on the first connection line and connected in series with the switching unit.

2. a control unit connected to the switching unit and configured to switch between the defibrillation mode and the potential measurement mode; 2. The defibrillation catheter system according to claim 1, wherein the control unit controls the switch element of the switching unit so that the switching unit is connected to the first connection line in the defibrillation mode and the switching unit is connected to the second connection line in the potential measurement mode.

3. the switching unit has a one-circuit two-contact switch, a common contact of the one-pole two-contact switch connected to the power source; a first contact of the single-pole, two-contact switch connected to the first resistor; 2. The defibrillation catheter system according to claim 1, wherein the second contact of the one-pole two-contact switch is connected to the electrocardiograph connection section without a resistor.

4. the defibrillation catheter system further includes a second resistor disposed on the second connection line and having a resistance value smaller than that of the first resistor; the switching unit has a one-circuit two-contact switch, a common contact of the one-pole two-contact switch connected to the power source; a first contact of the single-pole, two-contact switch connected to the first resistor; 2. The defibrillation catheter system according to claim 1, wherein the second contact of the one-pole, two-contact switch is connected to the second resistor.

5. the switching unit includes a first on / off switch connected to the first connection line and a second on / off switch connected to the second connection line, the first on-off switch is connected to the first resistor; 2. The defibrillation catheter system according to claim 1, wherein the second on / off switch is connected to the electrocardiograph connection section without a resistor.

6. the defibrillation catheter system further includes a second resistor disposed in the second connection line and connected in series with at least one of the one or more switches included in the switching unit, the second resistor having a resistance value smaller than that of the first resistor; the switching unit includes a first on / off switch connected to the first connection line and a second on / off switch connected to the second connection line, the first on-off switch is connected to the first resistor; 2. The defibrillation catheter system according to claim 1, wherein the second on / off switch is connected to the second resistor.

7. One end of the first connection line is connected to the switching unit, one end of the second connection line is connected to the switching unit, the other end of the first connection line and the other end of the second connection line are connected to each other at a connection portion, The defibrillation catheter system according to any one of claims 3 to 6, further comprising: a third connection line between the connection part and the electrocardiograph connection part; and a third resistor arranged on the third connection line and having a resistance value smaller than that of the first resistor.

8. 3. The defibrillation catheter system according to claim 1, wherein the resistance value of the first resistor is 10 kΩ or more and 10 MΩ or less.

9. 7. The defibrillation catheter system according to claim 4, wherein the resistance value of the second resistor is 50Ω or more and 150Ω or less.

10. 8. The defibrillation catheter system according to claim 7, wherein the resistance value of the third resistor is equal to or greater than 50 Ω and equal to or less than 150 Ω.

11. 5. The defibrillation catheter system according to claim 3, wherein the switching unit further includes a power supply side on / off switch disposed closer to the power supply than the one-circuit two-contact switch.

12. 7. The defibrillation catheter system according to claim 5, wherein the switching unit further includes a power supply side on / off switch that is disposed closer to the power supply than the first on / off switch and closer to the power supply than the second on / off switch.

Images