DESCRIPTION

Field of the invention

[0001]. The present invention generally relates to apparatuses and methods to treat target regions of tissue in organs.

[0002]. Particularly, the present invention relates to an electronic apparatus for delivering Coherent Sine Burst IRreversible Electroporation (IRE) energy to a biological tissue, wherein the electronic apparatus comprises a plurality of electrodes positionable either on or near the biological tissue to be treated and a power generator configured to generate an electric signal to energize each of said electrodes.

[0003]. The invention also relates to a method for controlling the plurality of electrodes in the electronic apparatus for delivering Coherent Sine Burst Irreversible Electroporation energy.

Background art

[0004]. Tissue ablation is used in numerous medical procedures to treat a patient. Ablation can be performed to remove or denature undesired tissue such as diseased cardiac cells. The ablation can be performed by passing energy, such as electrical energy, through one or more electrodes and causing tissue death where the electrodes are in contact. Ablation procedures can be performed on patients with any cardiac arrhythmia such as atrial fibrillation (AF) by ablating tissue in the heart.

[0005]. Radiofrequency ablation (RFA) is a medical procedure in which part of the electrical conduction system of the heart, tumor or other dysfunctional tissue is ablated using the heat generated from medium frequency alternating current, e.g. in the range of 350-500 kHz.

[0006]. Particularly, in this procedure an energy delivery device, such as a probe with or without a needle, is inserted into a target tissue to cause destruction of a target region of the cardiac tissue through the application of thermal energy. In fact, electrically induced thermal ablation such as RFA can be used to effectively and continuously locally ablate a tissue site as the energy delivery device is placed on the tissue surface. Although RFA can effectively ablate volumes of target tissue, there are limitations to this technique. One often cited problem using this procedure during cardiac ablation involves heat sink, a process whereby one aspect can include blood flow whereas the heat generated on the ablation element will be removed/dissipated by the cooler blood flows over the element. This heat dissipation effect can change both the shape and maximum volume of the tissue being ablated.

[0007]. More recently, to ablate cardiac or organ tissue, Pulsed Electric Fields (PEF) have been used as an alternative to the above-mentioned RFA.

Pulsed Electric Fields (PEF) refer to application of intermittent, high-intensity electric fields for short periods of time (micro or nanoseconds), which results in cellular and tissue electroporation. Electroporation is a process whereby an applied electric field (i.e. PEF) results in the formation of pores in cell membranes. Pore formation leads to permeabilization, which can be reversible or irreversible, depending upon parameters of the applied PEF.

[0008]. In reversible electroporation, cells remain viable, and underlies the basis of electrochemotherapy and gene electrotransfer. In contrast, with irreversible electroporation (IRE), cells and tissue are non-viable because of programmed cell death cascade activation.

[0009]. IRE is a well-established treatment for solid tumors. However, IRE may also be useful in cardiology, particularly for cardiac ablation, given limitations of current thermal based approaches.

[0010]. When used to ablate cardiac tissue, IRreversible Electroporation (IRE) involves the application of electrical pulses to targeted tissue in the range of microseconds to milliseconds that can lead to non-thermally produced defects in the cell membrane that are nanoscale in size. These defects can lead to a disruption of homeostasis of the cell membrane, thereby causing irreversible cell membrane permeabilization which induces cell necrosis, without raising the temperature of the tissue ablation zone.

[0011]. Typical PEF parameters to cause IRE include 10-90 pulses, with a pulse length of microseconds or nanoseconds (usually 100 ps), at a frequency of 1-10 Hz, and with an electric field between 500 and 3000 V/cm. See reference Elad Maor et al “Pulsed electric fields for cardiac ablation and beyond: A state-of-the-art review”, Heart Rhythm 2019; 16: 1112-1120).

[0012]. One challenge in designing PEF protocols is separating the effects electric fields can have on biological tissues. An electric field applied across tissue will induce heat by Joule’s first law, which states power of heating is proportional to resistance and square of the current. To overcome this and to solely obtain electroporation damage, most PEF protocols use ultrashort pulses (microseconds) at low frequency (1-10 Hz). This balances heating with the cooling effect of physiological heat conduction and convection, preventing significant rises in temperature.

[0013]. IRE performed with unipolar electrical pulses has the disadvantage of causing intense muscle contractions. Therefore, clinical applications of IRE require the administration of general anesthesia and neuroparalytic agents in order to eliminate the discomfort caused by muscle contractions seen during each pulse. However, receiving paralytic agents is undesirable for patients, and may deter them from seeking an electroporation based therapy.

[0014]. Electronic systems are known in the art for delivering IRreversible Electroporation (IRE) energy to a biological tissue, wherein these electronic systems are configured to generate high-frequency, bipolar waveforms for mitigating muscle contractions during electroporation based therapies.

[0015]. In particular, High-Frequency IRE (H-FIRE) is a technique for non-thermal tissue ablation that eliminates muscle contractions seen in IRE treatments performed with unipolar electric pulses. In fact, no visual or tactile evidence of muscle contraction was seen during H-FIRE at 250 kHz or 500 kHz. Therefore, H-FIRE can be performed clinically without the administration of paralytic agents.

[0016]. H-FIRE can involve the application of square wave electrical signals. For this purpose, it is known, for example, to use square wave signals centered at 500 kHz.

[0017]. However, rectangular waveforms comprise signal components having various frequencies and amplitudes that could create dangerous effects when IRE is used to specifically treat cardiac tissue. For example, a traditional IRE square wave signal has a 150Hz component at a voltage of around 6V, which poses a significant risk of heart stimulation.

[0018]. The issue with squarewave pulsed electric fields are the similarities to that of an ICD (Internal Cardiac Defibrillator): these types of devices cause significant heart tissue damage when discharged. Using squarewave pulsed electric field can cause heart tissue damage outside the desired zone. As such, sedation is required and square-wave delivery has to be synchronized with the R-wave of an ECG.

[0019]. It is therefore still strongly felt the need of providing an IRreversible Electroporation (IRE) based treatment for a biological tissue, especially the heart tissue, which avoids cardiac muscle stimulation and does not require sedation of the patients.

SUMMARY OF THE INVENTION

[0020]. It is the object of the present invention to provide an electronic apparatus for delivering Irreversible Electroporation (IRE) energy, particularly Coherent Sine Burst IRE, to a biological tissue to be treated, particularly a cardiac tissue, having structural and functional features such as to meet the aforementioned needs and overcome the drawbacks mentioned above with reference to the electronic systems of the prior art used for the same purpose.

[0021]. These and other objects are achieved by an electronic apparatus according to claim 1 .

[0022]. Particularly, the present invention provides for a novel electronic apparatus 100 for delivering Coherent Sine Burst Irreversible Electroporation energy, or IRE, to a biological tissue 1 to be treated, particularly a cardiac tissue.

[0023]. The electronic apparatus 100 comprises: a plurality of electrodes 3 positionable either on or near the biological tissue 1 to be treated; and a power generator 2 for supplying electric energy to each of the electrodes 3 of said plurality.

[0024]. It is a purpose of this invention, in certain embodiments, to provide the power generator 2 configured to generate an electric signal S to energize each of said electrodes 3.

[0025]. The electric signal S is formed by alternating over time a first electric signal S1 with a second electric signal S2; the first electric signal S1 is supplied to the electrodes 3 during a first time interval T 1 and the second electric signal S2 is supplied to the electrodes during a second time interval T2 subsequent to the first time interval T1 ; said first electric signal S1 is a continuous bipolar signal comprising two or more basic sine waves SB in said first time interval T1 , each basic sine wave consisting in one positive half-wave and one negative half-wave; said second electric signal S2 having an amplitude equal to zero in said second time interval T2.

[0026]. Applicant has verified that the electric signal S, generated by alternating over time the first electric signal S1 , comprising two or more basic sine waves, with the second electric signal S2, having amplitude equal to zero, does not generate cardiac muscle stimulation. Therefore, in a first aspect, patients do not have to be sedated. In a further aspect, the delivery of energy does not have to be synchronized with the hearts R-wave of an ECG.

[0027]. It is a further purpose of this invention to provide a method for controlling the plurality of electrodes in the electronic apparatus for delivering Coherent Sine Burst Irreversible Electroporation energy according to claim 26, wherein the electronic apparatus comprises a plurality of electrodes 3 and a power generator 2. The method involves generating by the power generator 2 an electric signal S for supplying electric energy to each of the electrodes 3 of said plurality, said electric signal S being formed by alternating over time a first electric signal S1 with a second electric signal S2, said first electric signal S1 is a continuous bipolar signal comprising two or more basic sine waves SB in a first time interval T 1 , each basic sine wave consisting in one positive half-wave and one negative half-wave, said second electric signal S2 having an amplitude equal to zero in a second time interval T2 subsequent to the first time interval T1. The method further comprising supplying said first electric signal S1 to the electrodes 3 of said plurality during the first time interval T 1 ; supplying said second electric signal (S2) to the electrodes (3) of said plurality during the second time interval (T2).

[0028]. It is a further purpose of this invention to provide an electronic apparatus 100 for delivering Irreversible Electroporation energy, or IRE, to a biological tissue 1 to be treated. The electronic apparatus comprises one or more electrodes 3 positionable either on or near the biological tissue 1 to be treated and a power generator 2 for supplying electric energy to said one or more electrodes 3; said power generator 2 is configured to generate an electric signal S to energize said one or more electrodes 3. [0029]. The electric signal S is formed by alternating over time a first electric signal S1 with a second electric signal S2; said first electric signal S1 is supplied to the one or more electrodes 3 during a first time interval T 1 and said second electric signal S2 is supplied to the one or more electrodes during a second time interval T2 subsequent to the first time interval T1 ; said first electric signal S1 has a periodic waveform in the first time interval T 1 ; said second electric signal S2 has an amplitude equal to zero in the second time interval T2.

[0030]. It is a further purpose of this invention to provide a power generator 2 for delivering Coherent Sine Burst Irreversible Electroporation energy, or IRE, to a biological tissue 1 to be treated. The power generator comprises a single control unit 200 and a power unit 201 for generating an electric signal S formed by alternating over time a first electric signal S1 with a second electric signal S2; the power unit 201 comprises a power module 202 driven by the single control unit 200 to generate said first electric signal S1 during a first time interval T1 and to generate said second electric signal S2 during a second time interval T2 subsequent to the first time interval T1 ; the first electric signal S1 is a continuous bipolar signal comprising two or more basic sine waves SB in said first time interval T1 , each basic sine wave consisting in one positive half-wave and one negative half-wave; the second electric signal S2 has an amplitude equal to zero in said second time interval T2.

[0031]. According to alternative embodiments, a method for the ablation of a biological tissue 1 is provided. The method involves the step of using the electronic apparatus 100 for delivering Coherent Sine Burst Irreversible Electroporation energy, or IRE, according to the invention.

[0032]. According to alternative embodiments, a method for the treatment of a pathology in a patient is provided. The method involves the step of performing the ablation of a biological tissue 1 of said patient by using the electronic apparatus 100 for delivering Coherent Sine Burst Irreversible Electroporation energy, or IRE, according to the invention. [0033]. According to alternative embodiments, a method for the ablation of a biological tissue 1 by delivering Irreversible Electroporation energy, or IRE, is provided. The method involves the step of applying to said biological tissue 1 an electric signal S comprising at least a sine wave signal.

[0034]. According to a preferred embodiment, said electric signal S is formed by alternating over time a first electric signal S1 with a second electric signal S2; said first electric signal S1 is applied during a first time interval T 1 and said second electric signal S2 is applied during a second time interval T2 subsequent to the first time interval T1 ; the first electric signal S1 is a continuous bipolar signal comprising two or more basic sine waves SB in said first time interval T1 , each basic sine wave consisting in one positive half-wave and one negative half-wave; the second electric signal S2 having an amplitude equal to zero in said second time interval T2, thereby causing the ablation of said biological tissue 1 .

[0035]. According to a further preferred embodiment, said first electric signal S1 has a frequency in the range of 25 - 49 kHz or in the range of 40 - 60 kHz.

[0036]. According to alternative embodiments, a method for the treatment of a pathology in a patient by delivering Irreversible Electroporation energy, or IRE, is provided. The method comprises the step of applying to a biological tissue 1 of said patient an electric signal S formed by alternating over time a first electric signal S1 with a second electric signal S2; said first electric signal S1 is applied during a first time interval T1 and said second electric signal S2 is applied during a second time interval T2 subsequent to the first time interval T1 ; the first electric signal S1 is a continuous bipolar signal comprising two or more basic sine waves SB in said first time interval T 1 , each basic sine wave consisting in one positive half-wave and one negative half-wave; the second electric signal S2 has an amplitude equal to zero in said second time interval T2, thereby causing the ablation of said biological tissue 1 .

[0037]. According to a preferred embodiment, the first electric signal S1 has a frequency in the range of 25 - 49 kHz or in the range of 40 - 60 kHz.

[0038]. Some advantageous embodiments are the subject of the dependent claims. Drawinqs

[0039]. Further features and advantages of the invention will become apparent from the description provided below of exemplary embodiment thereof, given by way of non-limiting example, with reference to the accompanying drawings, in which:

[0040]. - Figure 1 shows schematically an electronic apparatus for delivering

Coherent Sine Burst Irreversible Electroporation energy, or IRE, to a biological tissue according to the present invention, wherein the electronic apparatus comprises a plurality of electrodes positionable either on or near the biological tissue to be treated, and a power generator for supplying electric energy to each of the electrodes;

[0041]. - Figure 2 shows, with a block diagram, the power generator of the electronic apparatus of figure 1 comprising a single control unit and a power unit;

[0042]. - Figure 3 shows, with a diagram as a function of time, an example of electric signal generated by the power generator of figure 1 by alternating over time a first electric signal with a second electric signal;

[0043]. - Figure 4 shows at a higher resolution a portion of the diagram of figure 3 representing the first electric signal;

[0044]. - Figure 5 illustrates a Fourier Analysis of the first electric signal including eleven basic sine waves at 50KHz;

[0045]. - Figure 6 illustrates an example of the circuital structure of one of six power modules included in the power unit of the power generator of figure 2;

[0046]. - Figures 7, 8 and 9 show, with enlarged views, circuital portions of the power module circuital structure of figure 6;

[0047]. - Figures 10A and 10B show schematically an electronic apparatus for delivering Coherent Sine Burst Irreversible Electroporation energy, or IRE, to a biological tissue according to the present invention, wherein the electronic apparatus comprises a first and a second electrodes positionable either on or near the biological tissue to be treated, and a power generator, this power generator being configured to supply both electrodes, respectively, with sine-waves electrical signals “in phase” or with sine-waves electrical signals “out of phase”; [0048]. Figure 11 shows schematically a plurality of electrodes electrically supplied by the power generator of apparatus of figure 1 , wherein said electrodes are operatively associated to a catheter and positionable either on or near a myocardial tissue to be treated, and are configured to deliver combined bi-polar and uni-polar voltages or alternating uni-polar and bi-polar voltage fields.

[0049]. The same or similar elements are indicated in the drawings by the same reference numeral.

Description of some preferred embodiments

[0050]. The present invention can be understood more readily by reference to the following detailed description, examples, drawing, and their previous and following description. However, before the present devices, systems, and/or methods are disclosed and described, it is to be understood that this invention is not limited to the specific devices, systems, and/or methods disclosed unless otherwise specified, as such can, of course, vary. It is also to be understood that the terminology used herein is for the purpose of describing particular aspects only and is not intended to be limiting.

[0051]. The following description of the invention is provided as an enabling teaching of the invention in its best, currently known embodiment. To this end, those skilled in the relevant art will recognize and appreciate that many changes can be made to the various aspects of the invention described herein, while still obtaining the beneficial results of the present invention. It will also be apparent that some of the desired benefits of the present invention can be obtained by selecting some of the features of the present invention without utilizing other features. Accordingly, those who work in the art will recognize that many modifications and adaptations to the present invention are possible and can even be desirable in certain circumstances and are a part of the present invention.

[0052]. In accordance with a general embodiment, with reference to figure 1 , an electronic apparatus for delivering Coherent Sine Burst Irreversible Electroporation energy, or IRE, to a biological tissue 1 to be treated according to the present invention is globally denoted by reference numeral 100. [0053]. The electronic apparatus 100 comprises a plurality of electrodes 3 positionable either on or near the biological tissue 1 to be treated and a power generator 2 for supplying electric energy to each of the electrodes 3 of said plurality. Particularly, the electrodes 3 of said plurality, six electrodes 3 are shown in the example of figure 1 , are operatively associated to a catheter 4.

[0054]. In a preferred embodiment, the biological tissue 1 to be treated is a cardiac tissue.

[0055]. The power generator 2 is electrically connected to the electrodes 3, particularly with six wires 7, and is configured to generate an electric signal S to energize each of said electrodes 3, i.e. to apply voltage electric fields to the biological tissue 1 through the electrodes 3.

[0056]. In addition, the electronic apparatus 100 comprises a further electrode 5 acting as a return electrode for the voltage electrical fields applied to the biological tissue 1 . Particularly, this return electrode 5 or backplate is electrically connected to the power generator 2 through a respective return wire 6.

[0057]. In an alternative embodiment (not shown in the figures) the electronic apparatus 100 can comprise a single electrode 3 positionable either on or near the biological tissue 1 to be treated. The power generator 2 is electrically connected to this single electrode 3 and is configured to generate an electric signal S to energize said electrode 3, i.e. to apply voltage electric fields to the biological tissue 1 through the single electrode 3.

[0058]. In more detail, with reference to figures 3-4, the electric signal S is formed by alternating over time a first electric signal S1 with a second electric signal S2. The first electric signal S1 is supplied to the electrodes 3 during a first time interval T 1 and the second electric signal S2 is supplied to the electrodes 3 during a second time interval T2 subsequent to the first time interval T 1 .

[0059]. The first electric signal S1 is a continuous bipolar signal comprising two or more basic sine waves SB in said first time interval T1. Each basic sine wave consisting in one positive half-wave and one negative half-wave. The second electric signal S2 has an amplitude equal to zero in said second time interval T2. [0060]. For example, the electric signal S depicted in figure 3 comprises three electric signals S1 , wherein two of said first electric signals S1 are spaced from one another by the second electric signal S2 which is null in the second time interval T2.

[0061]. In an alternative embodiment, the first electric signal S1 comprises two or more basic sine waves SB repeated over said first time interval T 1.

[0062]. With the present invention, the Applicant proposes the use of an electric signal S for ablating the tissue 1 that consists of several sine wave bursts, i.e. a plurality of first electric signals S1 , spaced by cooling periods, i.e. the second electric signals S2, in which no electrical energy is transferred to the electrodes 3. The sine wave bursts are created in a way that avoids stimulation of the heart, even if applied for longer periods of time. This is obtained by choosing the waveforms such that the net voltage of harmonic waves created in a region between 1 Hz and 200 Hz is negligible. In fact, the frequency interval 1 Hz and 200 Hz has to be avoided in order to avoid heart stimulation.

[0063]. In more detail, the diagram of electric signal S shown in figure 3 includes three sine wave bursts, each spaced by a cooling period of 1 .5 msec.

[0064]. In figure 5, a Fourier Analysis diagram of the first electric signal S1 including eleven basic sine waves SB, for example at 50 KHz is depicted. Particularly, this Fourier Analysis diagram indicates that the voltage amplitude of the 50 kHz signal component, i.e. the desired component, is 67 dB higher than the 150 Hz signal component, which is the harmful component. In particular, a peak voltage of 1 .5 kV for the signal component at 50 kHz corresponds about a peak voltage of 0.0005 V for the signal component at 150 Hz, i.e. a peak voltage near to zero which does not create heart stimulation.

[0065]. In comparison, a traditional IRE square wave signal has a 150 Hz signal component at a voltage of around 6 V, which would create a significant risk of heart stimulation.

[0066]. In accordance with an embodiment, the first electric signal S1 has a frequency in the range of 25 - 49 kHz.

[0067]. In accordance with a further embodiment, the first electric signal S1 has a frequency in the range of 40 - 60 kHz.

[0068]. In accordance with an alternative embodiment, the first electric signal S1 comprises from two to fifteen basic sine waves SB in said first time interval T 1 .

[0069]. In fact, depending on tissue ablation requirements, when a voltage applied to the tissue 1 with the electric signal S is selected to be higher, the generator 2 provides the first electric signal S1 including fewer basic sine waves SB repeated over the first time interval T 1 , i.e. fewer cycles of the first S1 and second S2 electric signals are required. On the contrary, when a voltage applied to the tissue 1 with the electric signal S is selected to be lower, the generator 2 provides the first electric signal S1 including more basic sine waves SB repeated over said first time interval, i.e. the more the number of cycles of the first S1 and second S2 electric signals are required. Therefore, the voltage applied to the tissue 1 with the electric signal S can be obtained as a trade off between the number of cycles and the number basic sine waves SB repeated over said first time interval T 1 .

[0070]. In accordance with an alternative embodiment, the second time interval T2 of the second signal S2, i.e. the cooling period, has a duration from at least 1 millisecond to 1 second.

[0071]. In particular, the duration of the second time interval T2 can be changed based on requirements for heat dissipations.

[0072]. In accordance with an alternative embodiment, a peak-to-peak mean amplitude of each basic sine wave SB is in the range of 2.000 V to 20.000 V. The preferred amount is tissue dependent. In particular, upon power up of the power generator 2, the initial setting could be -2.5 kV and +2.5 kV before changing to accommodate the various tissue requirements.

[0073]. In general, according to the present invention, properties of the electric signal S can be changed as long as the amplitude of signal components below 200 Hz are negligible.

[0074]. In accordance with an alternative embodiment described with reference to figures 1-2, the power generator 2 comprises a single control unit 200 and a power unit 201 for generating the electric signal S. Particularly, the power unit 201 is electrically connected to all electrodes 3 of said plurality of electrodes.

[0075]. In accordance with an alternative embodiment, the power unit 201 is driven by the single control unit 200 to change the number of basic sine waves SB repeated over said first time interval T 1 to modify the electric energy level associated to the signal S to be supplied to the electrodes 3.

[0076]. In accordance with an alternative embodiment, the power unit 201 is driven by the single control unit 200 to change the duration of the second time interval T2 to modify the electric energy level associated to the signal S to be supplied to the electrodes.

[0077]. In accordance with an alternative embodiment, the power unit 201 comprises a power module 202 driven by the single control unit 200 to generate said first electric signal S1 during the first time interval T1 and to generate said second electric signal S2 during the second time interval T2.

[0078]. Particularly, the power module 202 comprises one or more of: a drive circuit block 203 controlled by the single control unit 200 for generating said first S1 or second S2 electric signal starting from drive signals PS1 , PS2 provided by the single control unit 200 or a signal null, respectively; a selecting block 204 selectively controlled by said drive circuit block 203 to change continuously the electric energy level associated to said electric signal S; a filtering and electrical isolation block 205, 206, 205’.

[0079]. In accordance with an alternative embodiment, the single control unit 200 comprises one or more of a Microprocessor 207 configured to control a variable High Voltage Power Supply block 208 and a Programmable Logic Controller block 209. The variable High Voltage Power Supply block 208 is configured to provide a supply voltage signal Vcc, Vcc1 to the power module 202 for generating the electric signal S. In more detail, the supply voltage signal comprises a first direct current power supply voltage Vcc and a second direct current power supply voltage Vcc1 . The first Vcc and second Vcc1 power supply voltage are in parallel with respective protection capacitors C10 and C2.

[0080]. The Programmable Logic Controller block 209 is configured to generate said drive signals PS1 , PS2 to control the drive circuit block 203 of the power module 202.

[0081]. The single control unit 200 further comprises on or more of:

-a Video interface and Push Button block 210, 210’ controlled by the Microprocessor 207 to set parameters of the electronic apparatus 100 and display the selected parameters; - a Watch Dog block 211 for controlling proper functioning of the Microprocessor 207; -an Audio interface block 212 for providing audio information representative of correctness of the electroporation process and/or errors occurred.

[0082]. In accordance with an alternative embodiment, the power unit 201 comprises one or more power modules 202 equal to each other. In the example of figure 2, the power unit 201 comprises six power modules 202. Each power module 202 is configured to generate and supply the electric signal S to one electrode 3.

[0083]. In accordance with an embodiment, at least one of the electrodes 3 of said plurality of electrodes is a monopolar electrode, and said monopolar electrode is electrically connected to only one power module 202 of the power unit 201 .

[0084]. In a further embodiment, at least two of said electrodes 3 of said plurality of electrodes are electrically connected to form bipolar electrodes, and said bipolar electrodes are electrically connected separately to a respective power module 202 selectable among the power modules of said power unit 201.

[0085]. In accordance with an embodiment, in order to provide either bipolar voltage or a combination of bipolar and unipolar voltage, the electric signals at the output of two or more power modules 202 of the power unit 201 have to be selected. For example, the power unit 201 comprises six power modules 202 equal to each other. Particularly, with reference to figure 2, from top to bottom, a first power module 2021 , a second power module 2022, a third power module 2023, a fourth power module 2024, a fifth power module 2025, a sixth power module 2026.

[0086]. Single pairs can be formed by power modules 2021 and 2022 or power modules 2022 and 2023 or power modules 2023 and 2024 or power modules 2024 and 2025 or power modules 2025 and 2026.

[0087]. The returns of all power modules 2021-2026 are connected together and correspond to the return wire 6.

[0088]. For example, to provide either bipolar voltage or a combination of bipolar and unipolar voltage, the electric signals S generated by the first 2021 , third 2023, fifth 2025 power modules are all at a same first phase value. The electric signals S generated by the second 2022, fourth 2024, sixth 2026 power modules are all at a second phase value, different from the first phase value. [0089]. According to an exemplary embodiment, when the difference between the first phase value and the second phase value is 60 degrees, the bipolar voltage generated by two adjacent power modules is the same as the unipolar voltage.

[0090]. In accordance with an alternative embodiment, the power generator 2 is powered by a battery or is connected to a standard wall outlet of an AC electrical power grid capable of producing 110 volts or 240 volts.

[0091]. In accordance with an alternative embodiment, the drive circuit block of each power module 202 comprises an amplifier circuit 203 in Emitter-Follower configuration.

[0092]. In order to generate the first electric signal S1 of said electric signal S, the amplifier circuit 203 is configured to amplify the drive signals generated by the single control unit 200. These drive signals comprise a first PS1 and a second PS2 pulsed signals supplied by the single control unit 200. In particular, the first pulsed signal PS1 comprises a first square wave, and the second PS2 pulsed signal comprises a second square wave wherein the second square wave is 180 degrees out of phase with respect to the first square wave.

[0093]. In order to generate the second electric signal S2 of said electric signal S, the single control unit 200 is configured to supply said amplifier circuit 203 with a respective drive signal null.

[0094]. In accordance with an alternative embodiment, the selecting block 204 of each power module 202 comprises a H-Bridge circuit 204.

[0095]. In order to generate the first electric signal S1 of said electric signal S, said H-Bridge circuit 204 is configured to combine the first PS1 and the second PS2 pulsed signals amplified by the amplifier circuit 203 to generate a combined signal CS having a square wave form.

[0096]. In accordance with an alternative embodiment, the filtering and electrical isolation block 205, 206, 205’ of each power module 202 comprises:

- a first series resonance filter 205 configured to generate a sine wave signal SW by converting the square wave combined signal CS generated at the output of the H- Bridge circuit 204;

- a transformer 206 configured to amplify said sine wave signal SW to generate a further sine wave signal SW1 ; - a second series resonance filter 205’ configured to generate the first electric signal S1 of said electric signal S to be supplied to the electrodes 3 by filtering the further sine wave signal SW1 .

[0097]. With reference to figures 6-7, a preferred embodiment of the amplifier circuit 203 in Emitter-Follower configuration is described in detail.

[0098]. The amplifier circuit 203 comprises a first 203’ and a second 203” amplifier circuit in Emitter-Follower configuration identical to each other. Each amplifier circuit 203’, 203” is connected between the first direct current power supply voltage Vcc and a ground potential or ground GND.

[0099]. The first amplifier circuit 203’ comprises a first input circuit M7, R1 , Q1 , Q3 configured to receive as input the first PS1 pulsed signal. Particularly, the first input circuit comprises a first MOSFET transistor M7 configured to receive the first pulsed signal PS1 at a gate terminal and having a respective source terminal connected to ground GND. The first input circuit also comprises a first resistor R1 connected between the first power supply voltage Vcc and a drain terminal of the first MOSFET transistor M7. The drain terminal of the first MOSFET transistor M7 is electrically connected to respective base terminals of first BJT transistors, particularly two BJT transistors, Q1 and Q3 connected (with their respective collector terminals) between the first power supply voltage Vcc and the ground GND in an Emitter-Follower configuration. The emitter terminals of said first BJT transistors Q1 and Q3 are connected to a respective first output terminal OU1 of the first amplifier circuit 203’.

[00100]. The second 203” amplifier circuit comprises a second input circuit M8, R4, Q2, Q4 configured to receive as input the second pulsed signal PS2. Particularly, the second input circuit comprises a second MOSFET transistor M8 configured to receive the second PS2 pulsed signal at a gate terminal and having a respective source terminal connected to ground GND. The second input circuit also comprises a second resistor R4 connected between the first power supply voltage Vcc and a drain terminal of the second MOSFET M8 transistor. The drain terminal of the second MOSFET transistor M8 is electrically connected to respective base terminals of second BJT transistors, particularly two second BJT transistors, Q2 and Q4 connected (with their respective collector terminals) between the first power supply voltage Vcc and the ground GND in an Emitter-Follower configuration. The emitter terminals of said second BJT transistors Q2 and Q4 are connected to a respective second output terminal OU2 of the second amplifier circuit 203”.

[00101]. The power module 202 comprises a first transformer circuit 230 interposed between the amplifier circuit or drive circuit block 203 and the H-Bridge circuit 204. In more detail, the transformer circuit 230 comprises an electrical transformer or isolator having a primary winding L1 and four secondary windings, particularly a first L2, second L3, third L4 and fourth L5 secondary windings.

[00102]. Terminals of the primary winding L1 of the first transformer circuit 230 are connected to the output terminals OU1 , OU2 of the first 203’ and second 203” amplifier circuits, respectively.

[00103]. The H-Bridge circuit 204 comprises a power inverter block 204 configured to generate at its output the combined signal CS having a square wave form starting from the second direct current power supply voltage Vcc1 and by combining the first PS1 and the second PS2 pulsed signals amplified by the amplifier circuit 203.

[00104]. In more detail, with reference to figures 6 and 8, an example of the power inverter block 204 of the H-Bridge type included in the power module 202 of the invention is described below.

[00105]. This power inverter block comprises a driving portion 204’ of the H-Bridge inverter and a power portion 204” of the H-Bridge inverter.

[00106]. In particular, the power portion 204” of the H-Bridge inverter 204 comprises:

- a first inverter branch B1 comprising a first M1 and a second M2 power Mosfet;

- a second inverter branch B2 comprising a third M3 and a fourth M4 power Mosfet.

[00107]. The first M1 and third M3 power Mosfet are connected between a power supply terminal at the second power supply voltage in direct current Vcc1 , through a resistor R5 of second direct current power supply voltage, and, respectively, a first 01 and a second 02 output terminals of the H-Bridge circuit 204.

[00108]. The second M2 and fourth M4 power Mosfet are connected between the aforementioned first 01 and second 02 output terminals of the H-Bridge circuit 204 and the ground potential GND. [00109]. The H-Bridge circuit comprises a power inverter 204 comprising a driving portion 204’. The driving portion 204’ of the H-Bridge inverter 204 is described in detail below.

[00110]. In particular, the gate terminal of the aforementioned first M1 power Mosfet is connected to one terminal of the first secondary winding L2 through a third resistor R8. The first 01 output terminal of the H-Bridge circuit 204 is connected to the gate terminal of the first power Mosfet M1 through a first diode D2 series connected to a fourth resistor R11. The other terminal of the first secondary winding L2 is directly connected to the first output terminal 01 of the H-Bridge circuit 204.

[00111]. Furthermore, the gate terminal of the third M3 power Mosfet is connected to one terminal of the third secondary winding L4 through a fifth resistor R3. The gate terminal of the third Mosfet M3 is connected to ground GND through a sixth resistor R13 series connected to a second diode D4. The other terminal of the third secondary winding L4 is directly connected to the second output terminal 02 of the H-Bridge circuit 204.

[00112]. In addition, the gate terminal of the second M2 power Mosfet is connected to one terminal of the second secondary winding L3 through a seventh resistor R9. The gate terminal of the second Mosfet M2 is connected to ground GND through a eighth resistor R10 series connected to a third diode D1. The other terminal of the second secondary winding L3 is directly connected to ground GND.

[00113]. In addition, the gate terminal of the fourth M4 power Mosfet is connected to one terminal of the fourth secondary winding L5 through a ninth resistor R7. The gate terminal of the fourth Mosfet M4 is connected to ground GND through a tenth resistor R12 series connected to a fourth diode D3. The other terminal of the fourth secondary winding L5 is directly connected to ground GND.

[00114]. It should be noted that the H-Bridge circuit 204 comprises the power inverter block 204 configured to generate the combined signal CS having a square wave form between the above mentioned first 01 and second 02 output terminals which are connected to each other with an output resistor R6.

[00115]. For example, the H-bridge circuit 204 is required to switch pulses at a voltage of +20 V or -20 V. However, the first M1 , second M2, third M3 and fourth M4 Mosfet transistors are only rated for a gate voltage of -7 V or more. Accordingly, the H-Bridge circuit 204 includes for each Mosfet transistor M1-M4 a respective diode, D1 , D2, D3, D4 connected to a resistor R10, R11 , R12, R13 for limiting the negative pulse to -7 V.

[00116]. After generating the combined signal CS having a square wave form at the H-bridge circuit 204, the power module 202 of the present invention comprises a first series resonance filter 205 for converting the combined signal CS into a sine wave signal SW.

[00117]. With reference to figure 6, the first series resonance filter 205 is connected between the output of the H-bridge circuit 204 and the transformer 206 configured to amplify said sine wave signal SW to generate the further sine wave signal SW1 . The transformer 206 comprises a first L6 winding and a second winding L8. Said further sine wave signal SW1 is provided between a respective first terminal of the second winding L8 of the transformer 206 and a respective second terminal connected to ground GND.

[00118]. In accordance with an exemplary embodiment, the transformer 206 is a 1 to 3 ratio step up isolation transformer with a high frequency ferrite core.

[00119]. In more detail, such first series resonance filter 205 comprises an inductance L14 series connected with a capacitor C1. The so obtained sine wave signal is then amplified by the transformer L6/L8. The values of inductance L14 and capacitor C1 is determined by the specific application to IRE.

[00120]. The first series resonance filter 205 is for example a band pass filter configured to filter all the harmonic components of the combined square wave signal CS except a base harmonic selected for the sine wave signal SW. For example, for a base harmonic of 40 kHz, typical values of inductance L14 and capacitor C1 are, for example: L14= 10 pH, C1= 1pF.

[00121]. Due to the high output voltage of the first sine wave electric signal S1 required for electroporation, the power module 202 of the present invention comprises also, advantageously, a second series resonance filter 205’.

[00122]. This second series resonance filter 205’ is required to have a significantly higher capacity than the series resonance filters known in the art, such as filters used for Radio Frequency Ablation or RFA. [00123]. This second series resonance filter 205’ is neither required in RFA generators known in the art nor in square wave PFA generators.

[00124]. According to an embodiment, this second series resonance filter 205’ is connected between the transformer 206 and a load R2 of the power module 202. Particularly, the second series resonance filter 205’ is connected between the first terminal of the second winding L8 of the transformer 206 and a load resistor R2. This load resistor R2 can be assimilated to the resistance associated to each electrode 3 of the electronic apparatus 100.

[00125]. Preferably, the second series resonance filter 205’ is a band pass filter configured to improve filtering of a base harmonic, for example of 40 kHz, selected for the further sine wave signal SW1 .

[00126]. In a preferred embodiment, the second series resonance filter 205’ comprises an inductive circuital portion 205A series connected to a capacitive circuital portion 205B. Both the inductive circuital portion 205A the capacitive circuital portion 205B are connected between the first terminal of the second winding L8 of the transformer 206 and the load resistor R2.

[00127]. In accordance with an exemplary embodiment, the inductive circuital portion 205A comprises four inductances, particularly a first L7, a second L9, a third L10 and a fourth L11 inductances. The first and second inductances L7-L9 are connected to each other in series, to form a first couple of inductances. The third and fourth inductances L10-L11 are connected to each other in series, to form a second couple of inductances. The two couples of inductances, L7-L9 and L10-L11 are connected to each other in parallel.

[00128]. Typical values are L7=L9=L10=L11 = 760 pH.

[00129]. In accordance with an exemplary embodiment, the capacitive circuital portion 205B of the second series of resonance filter 205’ comprises a plurality of capacitors, particularly seven capacitors in the example shown in figures 6 and 9, more particularly a first C3, a second C4, a third C5, a fourth C6, a fifth C7, a sixth C8 and a seventh C9 capacitors, that are connected to each other in series between the inductive circuital portion 205A and the load resistor R2.

[00130]. Typical values are C3=C4=C5=C6=C7=C8=C9=1 pF. [00131]. One relevant advantage provided by the amplifier circuit 203 in Emitter- Follower configuration is the low output impedance provided by this circuit. Particularly, this fact allows to maintain the output impedance of the H-Bridge circuit 204 of low values to avoid “ringing” due to the low pass filter associated to the first series resonance filter 205.

[00132]. In fact, if the H-Bridge circuit 204 is not driven, none of the devices in the bridge conduct and a high impedance is provided to the transformer 206. This acts as a RF switch as a high impedance is seen looking back into the output of that power module 202.

[00133]. Compared to the circuital solutions for power generators known in the art, for example the generators used in Radio-Frequency Ablation or RFA, the generators known in the art do not employ amplifier circuits in Emitter-Follower configuration, since in these circuits a sufficient amplification is already achieved at an output transformer.

[00134]. In addition, square wave generators used for PFA do not require low output impedance as the square wave is never converted into sine waves and “ringing” due to low pass filters is not an issue.

[00135]. The object of the present invention is also a method for controlling the plurality of electrodes in the electronic apparatus 100 for delivering Coherent Sine Burst Irreversible Electroporation energy, wherein the apparatus comprises a plurality of electrodes 3 and a power generator 2.

[00136]. The method comprising the step of generating by the power generator 2 an electric signal S for supplying electric energy to each of the electrodes 3 of said plurality. The electric signal S is formed by alternating over time a first electric signal S1 with a second electric signal S2. The first electric signal S1 is a continuous bipolar signal comprising two or more basic sine waves SB in a first time interval T1 , each basic sine wave consisting in one positive half-wave and one negative half-wave. The second electric signal S2 has an amplitude equal to zero in a second time interval T2 subsequent to the first time interval T 1 .

[00137]. The method further comprising the steps of:

- supplying said first electric signal S1 to the electrodes 3 of said plurality during the first time interval T 1 ; - supplying said second electric signal S2 to the electrodes 3 of said plurality during the second time interval T2.

[00138]. In accordance with an alternative embodiment, the power generator 2 comprises a single control unit 200 and a power unit 201 electrically connected to all electrodes 3 of said plurality of electrodes. The method further comprising the step of driving, by the single control unit 200, the power unit 201 :

- to change the number of basic sine waves SB repeated over said first time interval

T1 , or to

- change the duration of the second time interval T2 to modify the electric energy level

- associated to the signal S to be supplied to the electrodes 3.

[00139]. In accordance with an alternative embodiment, said step of driving comprises:

- in order to generate the first electric signal S1 of said electric signal S, amplifying a first PS1 and a second PS2 pulsed signals supplied by the single control unit 200 to the power unit 201 , said first pulsed signal PS1 comprising a first square wave, and said second PS2 pulsed signal comprising a second square wave, said second square wave being 180 degrees out of phase with respect to the first square wave;

- in order to generate the second electric signal S2 of said electric signal S, supplying, by the single control unit 200, the power unit 201 with the signal null. [00140]. In accordance with an alternative embodiment, in order to generate the first electric signal S1 of said electric signal S, the method further comprising: combining the first PS1 and the second PS2 pulsed signals to generate a combined signal CS having a square wave form;

- generating a sine wave signal SW by converting the square wave combined signal CS;

- amplifying said sine wave signal SW to generate a further sine wave signal SW1 ; filtering the further sine wave signal SW1 to generate the first electric signal S1 to be supplied to the electrodes 3. [00141]. In accordance with an alternative embodiment, a method is provided for controlling a single electrode 3 in an electronic apparatus 100 for delivering Coherent Sine Burst Irreversible Electroporation energy wherein the apparatus comprises a single electrode and a power generator 2 according to the present invention.

[00142]. With reference to figures 10A and 10B, alternative embodiments of the electronic apparatus 100 for delivering Coherent Sine Burst Irreversible Electroporation energy, or IRE, to a biological tissue 1 according to the present invention can be described.

[00143]. Particularly, the electronic apparatus 100 comprises a first 30 and a second 31 electrodes positionable either on or near the biological tissue 1 to be treated, and the power generator 2. As indicated in figure 10A, the power generator 2 is configured to supply both electrodes 30, 31 , respectively, with two sine-waves electrical signals Va and Vb “in phase”, particularly voltage signals. As indicated in figure 10B, the power generator 2 is configured to supply both electrodes 30, 31 , respectively, with two sine-wave electrical signals Va and Vb “out of phase”, particularly with a phase difference of 180 degrees.

[00144]. In more detail, with reference to figure 10A, the power generator 2 is configured to deliver unipolar power for Irreversible Electroporation to the tissue 1 driven by the difference in voltage between the first 30 and second 31 electrodes and the ground potential (0 V) associated to the return electrode 5.

[00145]. In this case, current flows from the first 30 and second 31 electrodes to ground, i.e. to the return electrode 5. There is no voltage difference between the first 30 and second 31 electrodes at any moment in time - thus no bipolar current flow.

[00146]. As the voltage oscillates between positive and negative peaks, the current moves to and from the ablation and return electrode 5.

[00147]. With reference to figure 10B, the power generator 2 of the invention is configured to deliver simultaneously both unipolar and bipolar power for Irreversible Electroporation to the tissue 1. In this case, voltage is applied both between each of the first 30 and the second 31 electrodes and the ground potential (0 V) associated to the return electrode 5 and through the same electrodes 30, 31 to each other. [00148]. These features of the electronic apparatus 100 of the invention can be described particularly with reference to figure 11 showing schematically a plurality of electrodes 3 electrically supplied by the power generator 2 (not shown) of the invention. These electrodes 3 are operatively associated to a catheter 4 positionable either on or near a myocardial tissue 1 to be treated.

[00149]. In an embodiment, the power generator 2 of the invention is configured to deliver to the electrodes 3 combined bi-polar and uni-polar voltages. A unipolar voltage is the voltage Va or Vb applied from each electrode 3 and the return electrode 5. Bipolar voltage, particularly voltage Va-Vb, is applied between two adjacent electrodes 3.

[00150]. In a different embodiment, the power generator 2 of the invention is configured to alternate uni-polar and bi-polar voltage fields, for example by time division multiplexing.

[00151]. For example, the power generator 2 of the invention uses 3500 Volts delivered to each electrode 3 during the first time interval T 1 of the electric signal S above mentioned.

[00152]. During the off-period of the electric signal S, i.e. during the second time interval T2, the output of each power module 202 is disconnected from the corresponding electrode 3.

[00153]. In more detail, the power generator 2 of the invention can operate to deliver IRE energy according to a sequence of three types of voltage delivery that repeats.

[00154]. In case of unipolar voltage only: voltage is applied from each electrode 3 to patient return electrode 5; this first step is followed by an off-period.

[00155]. In case of unipolar and bipolar voltage combined: in a first step voltage is applied from each electrode 3 to patient return electrode 5; this first step is followed by a second step in which voltage is applied across two adjacent electrodes; both steps are followed by an off period.

[00156]. According to an embodiment, by choosing the different combined, the ratio between bipolar and unipolar can be varied from 4 to 1 to all uni-polar. [00157]. By switching off the connection to the return electrode 5 in the electronic apparatus 100, and setting the phase shift of voltages Va and Vb to 180 degrees an all bi-polar mode can be produced.

[00158]. According to alternative embodiments, an object of the present invention is to provide an electronic apparatus 100 for delivering Irreversible Electroporation energy, or IRE, to a biological tissue 1 to be treated. The electronic apparatus comprises one or more electrodes 3 positionable either on or near the biological tissue 1 to be treated and a power generator 2 for supplying electric energy to said one or more electrodes 3; said power generator 2 is configured to generate an electric signal S to energize said one or more electrodes 3.

[00159]. The electric signal S is formed by alternating over time a first electric signal S1 with a second electric signal S2; said first electric signal S1 is supplied to the one or more electrodes 3 during a first time interval T 1 and said second electric signal S2 is supplied to the one or more electrodes during a second time interval T2 subsequent to the first time interval T1 ; said first electric signal S1 has a periodic waveform in the first time interval T 1 ; said second electric signal S2 has an amplitude equal to zero in the second time interval T2.

[00160]. According to an embodiment, the periodic waveform of the first electric signal S1 has a frequency in the range of 25 - 49 kHz.

[00161]. According to an alternative embodiment, the periodic waveform of the first electric signal S1 has a frequency in the range of 40 - 60 kHz.

[00162]. According to a further embodiment, the second time interval T2 of the second signal S2 has a duration from at least 1 milli-second to 1 second.

[00163]. According to alternative embodiments, a method for the ablation of a biological tissue 1 is provided. The method involves the step of using the electronic apparatus 100 for delivering Coherent Sine Burst Irreversible Electroporation energy, or IRE, according to the invention.

[00164]. According to an alternative embodiment, said biological tissue 1 to be ablated is selected from the group comprising: cardiac tissue, renal nerve, splenic nerve, tumors, cancer cells. [00165]. According to an alternative embodiment, said electronic apparatus 100 for delivering Coherent Sine Burst Irreversible Electroporation energy, or IRE, comprises a plurality of electrodes 3 positionable either on or near the biological tissue 1 to be ablated, and a power generator 2 configured to generate an electric signal S to energize each of said electrodes 3. Said electric signal S is formed by alternating over time a first electric signal S1 with a second electric signal S2; the first electric signal S1 is supplied to the electrodes 3 during a first time interval T 1 and the second electric signal S2 is supplied to the electrodes during a second time interval T2 subsequent to the first time interval T1 ; the first electric signal S1 is a continuous bipolar signal comprising two or more basic sine waves SB in said first time interval T 1 , each basic sine wave consisting in one positive half-wave and one negative halfwave; the second electric signal S2 has an amplitude equal to zero in said second time interval T2, thereby causing the ablation of said biological tissue 1 .

[00166]. According to an alternative embodiment, the first electric signal S1 has a frequency in the range of 25 - 49 kHz or in the range of 40 - 60 kHz.

[00167]. According to alternative embodiments, a method for the treatment of a pathology in a patient is provided. The method involves the step of performing the ablation of a biological tissue 1 of said patient by using the electronic apparatus 100 for delivering Coherent Sine Burst Irreversible Electroporation energy, or IRE, according to the invention.

[00168]. According to an alternative embodiment, said patology in a patient is selected from the group comprising: hypertension, heart failure, tumor.

[00169]. According to an alternative embodiment, said biological tissue 1 is selected from the group comprising: cardiac tissue, renal nerve, splenic nerve, tumors, cancer cells.

[00170]. According to alternative embodiments, a method for the ablation of a biological tissue 1 by delivering Irreversible Electroporation energy, or IRE, is provided. The method involves the step of applying to said biological tissue 1 an electric signal S comprising at least a sine wave signal.

[00171]. According to a preferred embodiment, said electric signal S is formed by alternating over time a first electric signal S1 with a second electric signal S2; said first electric signal S1 is applied during a first time interval T 1 and said second electric signal S2 is applied during a second time interval T2 subsequent to the first time interval T1 ; the first electric signal S1 is a continuous bipolar signal comprising two or more basic sine waves SB in said first time interval T1 , each basic sine wave consisting in one positive half-wave and one negative half-wave; the second electric signal S2 having an amplitude equal to zero in said second time interval T2, thereby causing the ablation of said biological tissue 1.

[00172]. According to a further preferred embodiment, said first electric signal S1 has a frequency in the range of 25 - 49 kHz or in the range of 40 - 60 kHz.

[00173]. According to an alternative embodiment, said biological tissue 1 is selected from the group comprising: cardiac tissue, renal nerve, splenic nerve, tumors, cancer cells.

[00174]. According to alternative embodiments, a method for the treatment of a pathology in a patient by delivering Irreversible Electroporation energy, or IRE, is provided. The method comprises the step of applying to a biological tissue 1 of said patient an electric signal S formed by alternating over time a first electric signal S1 with a second electric signal S2; said first electric signal S1 is applied during a first time interval T1 and said second electric signal S2 is applied during a second time interval T2 subsequent to the first time interval T1 ; the first electric signal S1 is a continuous bipolar signal comprising two or more basic sine waves SB in said first time interval T 1 , each basic sine wave consisting in one positive half-wave and one negative half-wave; the second electric signal S2 has an amplitude equal to zero in said second time interval T2, thereby causing the ablation of said biological tissue 1 .

[00175]. According to a preferred embodiment, the first electric signal S1 has a frequency in the range of 25 - 49 kHz or in the range of 40 - 60 kHz.

[00176]. According to an alternative embodiment, said patology in a patient is selected from the group comprising: hypertension, heart failure, tumor.

[00177]. The electronic apparatus 100 of present invention provides further relevant advantages.

[00178]. In particular, the power generator 2 configured to generate a first electric signal S1 including basic sinusoidal waves SB rely on transformers, particularly transformer 206 and first transformer circuit 230. Therefore, a high level of electrical isolation is ensured for the patient. [00179]. Furthermore, the electronic apparatus of the invention 100 ensures a high degree of flexibility for energy delivery by modifying the number of basic sine waves SB of the first electric signal S1 , the peak-to-peak amplitude of these sinewaves and the duration of the second time interval T2. Therefore, lengths and depths of lesions caused by the IRE procedure can be tailored.

[00180]. Electrodes delivering a sinusoidal-wave can be on, off or anything on the scale of zero degrees to 360 degrees out of phase.

[00181]. In addition, the Applicant has verified that the cost of components to design and manufacture the power generator 2 for generating a sinusoidal-wave is significant less than the cost for manufacturing generators of a square-wave known in the art.

LIST OF REFERENCE NUMERALS

100 Electronic apparatus

1 biological tissue

2 power generator

3 electrodes

30 first electrode

31 second electrode

4 catheter

5 further electrode, return electrode

6 return wire

7 wire

S electric signal

51 first electric signal

52 second electric signal

T 1 first time interval

T2 second time interval

SB basic sine wave

200 single control unit

201 power unit

202 power module

203 drive circuit block - amplifier circuit in emitter Follower configuration

204 selecting block - H-Bridge circuit - power inverter block

205 first series resonance filter

206 electrical isolation block -transformer

205’ second series resonance filter

207 Microprocessor

208 variable High Voltage Power Supply block

209 Programmable Logic Controller block

210 Video interface block

210’ Push Button block

211 Watch Dog block

212 Audio interface block -S O -

230 first transformer circuit

Vcc supply voltage signal - first direct current power supply voltage

Vcc1 supply voltage signal - second direct current power supply voltage

GND ground potential

PS1 first pulsed signal

PS2 second pulsed signal

CS combined signal

SW sine wave signal

SW1 further sine wave signal

203’ first amplifier circuit

203” second amplifier circuit

M7 first MOSFET transistor

R1 first resistor

Q1 , Q3 first BJT transistors

Q2, Q4 second BJT transistors

M8 second MOSFET transistor

R4 second resistor

OU1 first output terminal of the first amplifier circuit 203’

OU2 second output terminal of the second amplifier circuit 203”

207 first transformer circuit

L1 primary winding

L2 first secondary winding

L3 second secondary winding

L4 third secondary winding

L5 fourth secondary winding

204’ driving portion of the H-Bridge inverter

204” power portion of the H-Bridge inverter

B1 first inverter branch

B2 second inverter branch

M 1 first power Mosfet

M2 second power Mosfet

M3 third power Mosfet M4 fourth power Mosfet

R5 resistor of second direct current power supply voltage

01 first output terminal

02 second output terminal

R8 third resistor

D2 first diode

R11 fourth resistor

R3 fifth resistor

R13 sixth resistor

D4 second diode

R9 seventh resistor

R10 eighth resistor

D1 third diode

R7 ninth resistor

R12 tenth resistor

D3 fourth diode

R6 output resistor

L6 first winding of transformer 206

L8 second winding of transformer 206

L14 inductance

C1 capacitor

R2 load resistor

205A inductive circuital portion

205B capacitive circuital portion

L7 first inductance

L9 second inductance

L10 third inductance

L11 fourth inductance

C3 first capacitor

C4 second capacitor

C5 third capacitor

C6 fourth capacitor C7 fifth capacitor

C8 sixth capacitor

C9 seventh capacitor

C2, C10 protection capacitors

Va, Vb sine-wave electrical signals

2021 first power module

2022 second power module

2023 third power module

2024 fourth power module

2025 fifth power module

2026 sixth power module.