WO2026015502A1

WO2026015502A1 - Implantable medical systems with simultaneous actuation and charging and associated devices and methods

Info

Publication number: WO2026015502A1
Application number: PCT/US2025/036744
Authority: WO
Inventors: Peter ANDRIOLA
Original assignee: Shifamed Holdings LLC
Current assignee: Shifamed Holdings LLC
Priority date: 2024-07-08
Filing date: 2025-07-08
Publication date: 2026-01-15
Anticipated expiration: 2027-01-08

Abstract

Medical systems with simultaneous actuation and charging, and associated devices and methods are disclosed herein. In some embodiments, a method of simultaneously powering first and second power transfer coils having first and second resonant frequency ranges, the first and second power transfer coils being implanted within a patient, is disclosed. The method can comprise determining a coupling coefficient between the first power transfer coil and the second power transfer coil, and, based at least in part on the determined coupling coefficient, selecting a driving frequency for an external power source that induces (i) a first activation response level in the first power transfer coil above a first threshold, and (ii) a second activation response level in the second power transfer coil above a second threshold. The driving frequency can have a frequency value within one, but not both, of the first resonant frequency range or the second resonant frequency range.

Description

IMPLANTABLE MEDICAL SYSTEMS WITH SIMULTANEOUS ACTUATION AND CHARGING AND ASSOCIATED DEVICES AND METHODS

CROSS-REFERENCE TO RELATED APPLICATION(S)

[0001] The present application claims the benefit of U.S. Provisional Patent Application No. 63/668,431, filed July 8, 2024, the disclosure of which is incorporated herein by reference in its entirety.

TECHNICAL FIELD

[0002] The present technology generally relates to medical systems and, in particular, to implantable medical devices with simultaneous actuation and charging.

BACKGROUND

[0003] Implantable medical devices can be used to treat a variety of patient conditions. For example, implantable shunting systems are widely used to shunt fluid from a first body region/cavity to a second body region/cavity. The flow of fluid through the shunting systems is primarily controlled by the pressure gradient across the shunt lumen and the geometry (e.g., size) of the shunt lumen. Some shunting systems include multiple power transfer coils, such as a first power transfer coil for recharging and a second power transfer coil for adjusting the geometry of the shunt lumen. Different power transfer coils can be tuned to operate at different resonant frequencies such that different power transfer coils can be selectively and independently activated.

BRIEF DESCRIPTION OF THE DRAWINGS

[0004] Many aspects of the present technology can be better understood with reference to the following drawings. The components in the drawings are not necessarily drawn to scale. Instead, emphasis is placed on illustrating clearly the principles of the present technology. Furthermore, components can be shown as transparent in certain views for clarity of illustration only and not to indicate that the component is necessarily transparent. Components may also be shown schematically.

[0005] FIG. 1 is a schematic block diagram of a medical system configured in accordance with select embodiments of the present technology. [0006] FIG. 2 is a perspective view of an implantable medical device configured in accordance with select embodiments of the present technology.

[0007] FIG. 3 is a front view of a medical system configured in accordance with select embodiments of the present technology.

[0008] FIG. 4 is a schematic circuit diagram of a medical system configured in accordance with select embodiments of the present technology.

[0009] FIG. 5 is a graph illustrating activation response of a first power transfer coil in accordance with select embodiments of the present technology.

[0010] FIG. 6 is a graph illustrating activation response of a second power transfer coil in accordance with select embodiments of the present technology.

[0011] FIG. 7 is a flowchart illustrating a method for operating an implantable medical device in accordance with select embodiments of the present technology.

[0012] FIG. 8 is a flowchart illustrating a method for designing an implantable medical device in accordance with select embodiments of the present technology.

DETAILED DESCRIPTION

[0013] The present technology is generally directed to medical systems with simultaneous actuation and charging. In many of the embodiments described herein, a medical system includes an implantable medical device with a first power transfer coil and a second power transfer coil. The first and second power transfer coils can be tuned to operate at different resonant frequencies for selective and independent activation. The first and second power transfer coils can be generally or substantially coplanar, coaxial, similar in size, and/or the like. As described in throughout this Detailed Description, configuring the first and second power transfer coils to share certain physical properties can allow simultaneous actuation and charging of the implantable medical device using a single drive frequency notwithstanding the different resonant frequencies of the first and second power transfer coils.

[0014] The terminology used in the description presented below is intended to be interpreted in its broadest reasonable manner, even though it is being used in conjunction with a detailed description of certain specific embodiments of the present technology. Certain terms may even be emphasized below; however, any terminology intended to be interpreted in any restricted manner will be overtly and specifically defined as such in this Detailed Description section. Additionally, the present technology can include other embodiments that are within the scope of the examples but are not described in detail with respect to FIGS. 1-8.

[0015] Reference throughout this specification to “one embodiment” or “an embodiment” means that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment of the present technology. Thus, the appearances of the phrases “in one embodiment” or “in an embodiment” in various places throughout this specification are not necessarily all referring to the same embodiment. Furthermore, the particular features or characteristics may be combined in any suitable manner in one or more embodiments.

[0016] As used herein, the use of relative terminology, such as “about,” “approximately,” “substantially,” and the like refer to the stated value plus or minus ten percent. For example, the use of the term “about 100” refers to a range of from 90 to 110, inclusive. In instances in which the context requires otherwise and/or relative terminology is used in reference to something that does not include a numerical value, the terms are given their ordinary meaning to one skilled in the art.

[0017] FIG. 1 is a schematic block diagram of a medical system 100 configured in accordance with select embodiments of the present technology. The medical system 100 can include a driving device 110 and an implantable medical device 120 that can be activated (e.g., actuated, recharged) via the driving device 110. The driving device 110 can include a driving coil 130, a controller 132, and a power source 134, and the implantable medical device 120 can include a first power transfer coil 140 and a second power transfer coil 150. In some embodiments, the implantable medical device 120 comprises an implantable shunting device, the first power transfer coil 140 is activated to adjust a geometry of a shunting lumen of the shunting device, and the second power transfer coil 150 is activated to charge and/or power electrical components of the shunting device.

[0018] In some embodiments, the driving device 110 comprises an external device that can activate the implantable medical device 120 implanted inside a patient from outside of/extemal to the patient’s body. In other embodiments, the driving device 110 comprises a catheter or other medical device intended for at least partial insertion into the patient such that the driving coil 130 can be brought into closer proximity to the implantable medical device 120 during operation (e.g., actuation, recharging, etc.) than arrangements in which the driving device 110 comprise external device completely outside of/external to the patient.

[0019] During operation, upon bringing the driving coil 130 in sufficient proximity to the first power transfer coil 140 and/or the second power transfer coil 150, current flowing through the driving coil 130 (e.g., provided by the power source 134 and modulated by the controller 132) can induce current to flow in the first power transfer coil 140 and/or the second power transfer coil 150, respectively. Power can be transferred via induction and/or resonance (e.g., the driving coil 130 can comprise a radiofrequency (RF) coil that emit RF pulses). In some embodiments, the first power transfer coil 140 and the second power transfer coil 150 are designed to operate at and/or have different resonant frequencies such that the first coil 140 and the second coil 150 can be selectively and independently activated. For example, in one embodiment, the first power transfer coil 140 can have a first resonant frequency and the second power transfer coil 150 can have a second resonant frequency less than the first resonant frequency. By operating the controller 132 to modulate the frequency emitted by the driving coil 130, a user can choose which of the coils (first power transfer coil 140 or second power transfer coil 150) to activate.

[0020] However, activating each of the first and second power transfer coils 140 and 150 separately can be time-consuming, leading to long medical procedures (e.g., for implantation, recharging, actuation). Therefore, it can be desirable to simultaneously activate the coils 140 and 150 and thereby shorten procedure time. In accordance with select embodiments of the present technology, the driving coil 130 can be operated at a single driving frequency, and more particularly at the greater of (i) the resonant frequency of the first power transfer coil 140 and (ii) the resonant frequency of the second power transfer coil 150, to simultaneously activate the first and second coils 140 and 150.

[0021] As discussed in further detail below with reference to FIGS. 4-6, the effectiveness of the simultaneous activation of the first and second power transfer coils 140 and 150 can at least partially depend on the coupling coefficient (denoted as k) between the first and second power transfer coils 140 and 150. The coupling coefficient & represents the degree of coupling between two coils or circuits, and ranges between 0 (no mutual inductance; perfectly decoupled) and 1 (maximum mutual inductance; perfectly coupled). The k value can depend on, for example, the physical position (e.g., distance) and orientation of the coils relative to each other, the geometry and size of the coils, and the permeability of the materials surrounding the coils, etc. There can exist an optimal k value for simultaneous activation of the first and second power transfer coils 140 and 150. Therefore, once the optimal k value is identified, the first and second power transfer coils 140 and 150 can be designed and arranged to achieve the identified optimal k value. However, due to anatomical and specific absorption rate (SAR) considerations, the geometrical designs of the first and second power transfer coils 140 and 150 for achieving the optimal k value can be limited. For example, in some embodiments, the first power transfer coil 140 and the second power transfer coil 150 are configured to share one or more physical properties. For example, the first power transfer coil 140 and the second power transfer coil 150 can be generally or substantially coplanar, coaxial, similar in size, and/or the like.

[0022] FIG. 2 is a perspective view of an implantable medical device 220 configured in accordance with select embodiments of the present technology. The implantable medical device 220 can be an example of the implantable medical device 120 of FIG. 1, and similarly numbered components can be similar in structure and/or function. In the illustrated embodiment, for example, the implantable medical device 220 comprises an implantable shunting system including a first power transfer coil 240, a second power transfer coil 250, first and second canisters 260a, 260b (collectively referred to as “the canisters 260”), and an actuation element 270 (schematically illustrated).

[0023] The first power transfer coil 240 can include one or more wires shaped to fomi a first plurality of petals or appendages 242 and a second plurality of petals or appendages 244. Each of the petals 242, 244 can comprise a portion of the wire in the shape of a “V” pointing radially outward. In some embodiments, a portion of the first power transfer coil 240 is coated with silver or other highly conductive material to facilitate current flow therethrough. The second power transfer coil 250 can include a spiral of wire lying on a plane, and the number of loops forming the second power transfer coil 250 can vary (e.g., 5 loops, as shown). FIG. 2 illustrates the first plurality of petals 242 and the second plurality of petals 244 lying adjacent but on opposite sides of the second power transfer coil 250. Also, the first power transfer coil 240 and the second power transfer coil 250 can define an adjustable shunting lumen 222 of the implantable medical device 220. Additional details regarding power transfer coils suitable for use with the implantable medical device 220 are described in International Patent Application PCT/US2023/85189, the disclosure of which is incorporated by reference herein in its entirety. [0024] The actuation element 270 can be positioned generally within the first power transfer coil 240 and the second power transfer coil 250, and operably coupled to the first power transfer coil 240. The actuation element 270 can define a shunting lumen 222 and can adjust the size thereof. For example, current induced in the first power transfer coil 240 (e.g., induced by the driving coil 130 of FIG. 1) can flow to and resistively heat the actuation element 270. In embodiments in which the actuation element 270 is made from a shape memory material (e.g., Nitinol), this resistive heating may heat the shape memory actuation element above its transition temperature and drive the material phase transformation that induces a geometry change in the shunting lumen 222. Additional details regarding resistively heating actuation elements via induction are described in International Patent Application PCT/US2021/55191, the disclosure of which is incorporated by reference herein in its entirety.

[0025] The canisters 260 can house one or more batteries, sensors (e.g., pressure sensors, temperature sensors), and/or other electrical components. The electrical components inside the canisters 260 can be electrically coupled to the second power transfer coil 250 such that current induced therein (e.g., induced by the driving coil 130 of FIG. 1) can power and/or recharge the electrical components. For example, the wire forming the spiral of the second power transfer coil 250 can extend into each of the canisters 260. In some embodiments, the implantable medical device 220 further includes a membrane (e.g., made from PTFE) covering the first power transfer coil 240, the second power transfer coil 250, the actuation element 270, and/or the canisters 260. The membrane can be fluidically impermeable or at least substantially fluidically impermeable to blood and/or other bodily fluids, thereby protecting the first power transfer coil 240, the second power transfer coil 250, the actuation element 270, and/or the canisters 260.

[0026] FIG. 3 is a front view of a medical system 300 configured in accordance with select embodiments of the present technology. The medical system 300 can be an example of the medical system 100 of FIG. 1, and similarly numbered components can be similar in structure and/or function. As shown, the medical system 300 can include a charging device 310 and the implantable medical device 220. The driving device 310 can include a driving coil 330. As shown, the driving coil 330 can be positioned adjacent (and parallel to) the power transfer coil 240 for transferring power thereto via induction and/or resonance. [0027] Referring to FIGS. 2 and 3 together, the driving coil 330 can be operated to emit energy at a driving frequency at or substantially at the greater of (i) the resonant frequency of the first power transfer coil 240 and (ii) the resonant frequency of the second power transfer coil 250. In some embodiments, doing so can induce current in both coils 240 and 250, notwithstanding the fact that the coils 240 and 250 may have different resonant frequencies. For example, the driving coil 330 can induce current in the coil with the greater resonant frequency (e.g., due to operation of the driving coil 330 at that resonant frequency), and coil coupling between the coils 240 and 250 can cause the current in the coil with the greater resonant frequency to induce current in the coil with the smaller resonant frequency.

[0028] Also, as shown in FIG. 2, the first power transfer coil 240 and the second power transfer coil 250 can share certain physical properties that can facilitate such coil coupling. More specifically, the first and second pluralities of petals 242, 244 lie adjacent and on opposite sides of the second power transfer coil 250 with a relatively small axial offset, with portions of the first power transfer coil 240 interconnecting the first and second pluralities of petals 242, 244 lying on the same plane as the second power transfer coil 250 (e.g., substantially coplanar). Also, the first power transfer coil 240 and the second power transfer coil 250 are both generally annular in shape and centered about the lumen 222 (e.g., substantially coaxial). Furthermore, the tips of the first and second pluralities of petals 242, 244 extend to a radius similar to the outer radius of the spiral of wire forming the second power transfer coil 250 (e.g., substantially similar in size).

[0029] FIG. 4 is a schematic circuit diagram of a medical system 400 configured in accordance with select embodiments of the present technology. The medical system 400, for example, can be an example circuit diagram of the medical system 100 of FIG. 1, and similarly numbered components can be similar in structure and/or function. As shown, the medical system 400 can include a driving device 410 having a driving circuit 430, and an implantable medical device 420 having a first power transfer circuit 440 and a second power transfer circuit 450. The driving circuit 430 can include a driving inductor 432, a power source 434, and a resistor R1 (e.g., resistance associated the driving circuit 430) coupled in series. The first power transfer circuit 440 can comprise an RLC circuit including a first inductor 442, a first capacitor Cl, and a resistor R2 (e.g., resistance associated the first power transfer circuit 440) coupled in series. The second power transfer circuit 450 can comprise an RLC circuit including a second inductor 452, a second capacitor C2, and a resistor R3 (e.g., resistance associated the second power transfer circuit 450) coupled in series.

[0030] The first power transfer circuit 440 and the second power transfer circuit 450 can have different resonant frequencies. For example, the first power transfer circuit 440 can have a first resonant frequency ranging between 10-20 MHz or 12-15 MHz (e.g., 13.56 MHz), and the second power transfer circuit 450 can have a second resonant frequency ranging between 1-10 MHz or 5-8 MHz (e.g., 6.78 MHz). Therefore, the driving inductor 432, which can be operated at a single frequency at any given time, can induce current in either the first power transfer circuit 440 or the second power transfer circuit 450, depending on which resonant frequency is matched.

[0031] However, when the first power transfer circuit 440 and the second power transfer circuit 450 share certain physical properties as discussed above, each of the first and second circuits 440 and 450 is sufficiently affected by the magnetic flux around the other circuit. This results in coil coupling (e.g., mutual inductance) between the first and second circuits 440 and 450 such that when the driving device is operated at the resonant frequency of, e.g., the first power transfer circuit 440, current is induced in the circuit 440 and the resulting magnetic field generated by the circuit 440 induces current in the second power transfer circuit 450. As mentioned previously, the degree of coil coupling is represented by the coupling coefficient k that can range between 0-1. In FIG. 4, the coupling coefficient between the circuits 440 and 450 is represented as k\. The value of can be determined by the design of the implantable medical device 420 (e.g., the physical position (e.g., distance) and orientation of the circuits 440 and 450 relative to each other, the geometry and size of the circuits 440 and 450, the permeability of the materials surrounding the circuits 440 and 450, etc.). As also mentioned above, the design of the implantable medical device can be limited by anatomical and/or SAR considerations.

[0032] FIG. 5 is a graph illustrating activation response of a first power transfer coil (e.g., the first power transfer coil 240, the first power transfer circuit 440) in accordance with select embodiments of the present technology. FIG. 6 is a graph illustrating activation response of a second power transfer coil (e.g., the second power transfer coil 250, the second power transfer circuit 450) in accordance with select embodiments of the present technology. Referring to FIGS. 5 and 6 together, the x-axis represents the driving frequency provided by a driving coil (e.g., the driving coil 330, the driving circuit 430) and the y-axis represents the activation response level of the first power transfer coil and the second power transfer coil, respectively.

[0033] Also, FIGS. 5 and 6 each plot multiple activation responses for various fa values (0, 0.25, 0.5, 0.75, 1), which can be adjusted by adjusting the design of, e.g., the implantable medical device. Notably, the plots show bumps primarily within a first frequency range FR1 (e.g., between 4-6 MHz) that may correspond to the resonant frequency of the second power transfer coil and within a second frequency range FR2 (e.g., between 10-20 MHz) that may correspond to the resonant frequency of the first power transfer coil. The activation response level for all k values are at or near zero when the driving frequency is outside of FR1 and FR2. Therefore, the discussion below focuses on cases when the driving frequency is within FR1 or FR2.

[0034] Referring first to FIG. 5, the graph shows that the activation response level of the first power transfer coil is minimal or negligible when the driving frequency is within FR1 for all fa values. Thus, in embodiments in which the first power transfer coil actuates an actuation element (e.g., the actuation element 270 of FIG. 2) to adjust the geometry (e.g., size) of a shunting lumen (e.g., the shunting lumen 222), a driving frequency within FR1 may be insufficient to properly actuate the actuation element and adjust the lumen geometry. By contrast, the graph of FIG. 5 shows that the activation response level of the first power transfer coil is significantly higher when the driving frequency is within FR2 for k values of 0, 0.25, and 0.5, but remains low for JC values of 0.75 and 1. Therefore, based on FR2 which corresponds to the resonant frequency of the first power transfer coil, the graph of FIG. 5 indicates a maximum fa value of 0.5, but not a minimum lvalue.

[0035] Referring next to FIG. 6, the graph shows that the activation response level of the second power transfer coil is high when the driving frequency is within FR1 for all ki values. Thus, in embodiments in which the second power transfer coil is operably coupled to charge and/or power electrical components of an implantable medical device (e.g., the electrical components housed in the canisters 260 of the implantable medical device 220), a driving frequency within FR1 is expected to be sufficient to properly charge and/or power electrical components using the second power transfer coil. By contrast, the graph of FIG. 6 shows that the activation response level of the second power transfer coil is relatively or sufficiently high when the driving frequency is within FR2 only when fa is 0.5, and is low for fa values of 0, 0.25, 0.75, and 1. Therefore, based on FR1 which corresponds to the resonant frequency of the second power transfer coil, the graph of FIG. 6 indicates neither a minimum nor maximum fci value.

[0036] Referring to FIGS. 5 and 6 together, the graphs indicate that a driving frequency within FR1, corresponding to the resonant frequency of the second power transfer coil, may not be used to simultaneously activate both coils, but that a driving frequency within FR2 may be used to simultaneously activate both coils. In the particular illustrated example, given the maximum /« value of 0.5 based on the graph of FIG. 5 within FR2 and the fact that only a kA value of 0.5 results in a sufficiently high activation response level by the second power transfer coil, 0.5 can be deemed the optimal kA value of those plotted. One of ordinary skill in the art will appreciate that the values presented in FIGS. 5 and 6 are merely examples, and that in other embodiments of power transfer coils, the resonant frequencies of the coils (and thus FR1 and FR2) and the optimal lvalue can be different (e.g., 0.1, 0.4, 0.9).

[0037] As mentioned above, because the kA value is determined by the design of the coils, upon identifying the optimal kA value as discussed herein, the design of the coils can be configured to provide the identified optimal value. In some embodiments, anatomical and SAR considerations can constrain what designs can be implemented to achieve the identified optimal kA value. For example, as discussed above, the pair of coils can be arranged to be generally or substantially coplanar, coaxial, similar in size, and/or the like. Designing the coils to have the identified optimal kA value can enable simultaneous activation of both coils using a single driving frequency. In embodiments in which the first coil actuates an actuation element and the second coil is operably coupled to electrical components (e.g., as illustrated in FIG. 2), the single driving frequency (e.g., at the greater resonant frequency of the two coils) can simultaneously adjust the geometry of the lumen and charge and/or power the electrical components. In some embodiments, charging while adjusting is expected to shorten procedure times while also leaving the implantable medical device fully charged.

[0038] FIG. 7 is a flowchart illustrating a method 700 for operating an implantable medical device in accordance with some embodiments of the present technology. While the steps of the method 700 are described below in a particular order, one or more of the steps can be performed in a different order or omitted, and the method 700 can include additional and/or alternative steps. Additionally, although the method 700 may be described below with reference to the embodiments of the present technology described herein, the method 700 can be performed with other embodiments of the present technology.

[0039] The method 700 begins at block 702 by positioning a driving coil (e.g., the driving coil 130 of FIG. 1) adjacent a first power transfer coil (e.g., the first power transfer coil 140) and a second power transfer coil (e.g., the second power transfer coil 150) of an implantable medical device (e.g., the implantable medical device 120). The first and second power transfer coils can be, for example, substantially coplanar and coaxial. In some embodiments, the first and second power transfer coils are substantially similar in size (e.g., have similar maximum dimensions). The first power transfer coil can have a first resonant frequency (e.g., between 10-20 MHz), and the second power transfer coil can have a second resonant frequency (e.g., between 1-10 MHz) less than the first resonant frequency.

[0040] At block 704, the method 700 continues by operating the driving coil at the first resonant frequency, thereby activating the first power transfer coil. Activating the first power transfer coil can, in turn, activate the second power transfer such that operating the driving coil at the first resonant frequency simultaneously activates the first and second power transfer coils. In some embodiments, activating the first power transfer coil adjusts a geometry of a shunting lumen (e.g., the shunting lumen 222 of FIG. 2) of the implantable medical device. For example, the geometry of the shunting lumen can be adjusted via resistive heating thereof. In some embodiments, activating the second power transfer coil charges and/or powers electrical components (e.g., housed in the canisters 260 of FIG. 2) of the implantable medical device.

[0041] In some embodiments, the method 700 further comprises arranging the first and second power transfer coils relative to one another based on an optimal coupling coefficient between the first and second power transfer coils. In some embodiments, the optimal coupling coefficient is identified by (i) generating a first plot of activation response levels of the first power transfer coil at a range of frequencies for a plurality of coupling coefficient values (e.g., the graph of FIG. 5), (ii) generating a second plot of activation response levels of the second power transfer coil at the range of frequencies for the plurality of coupling coefficient values (e.g., the graph of FIG. 6), and (iii) selecting the optimal coupling coefficient among the plurality of coupling coefficient values based on the generated first plot and the generated second plot. [0042] FIG. 8 is a flowchart illustrating a method 800 for designing an implantable medical device in accordance with some embodiments of the present technology. The implantable medical device can include a first power transfer coil and a second power transfer coil. While the steps of the method 800 are described below in a particular order, one or more of the steps can be performed in a different order or omitted, and the method 800 can include additional and/or alternative steps. Additionally, although the method 800 may be described below with reference to the embodiments of the present technology described herein, the method 800 can be performed with other embodiments of the present technology.

[0043] The method 800 begins at block 802 by plotting a plurality of first activation response levels of the first power transfer coil against a range of driving frequencies. Each of the plurality of first activation response levels can correspond to one of a plurality of coupling coefficients between the first power transfer coil and the second power transfer coil.

[0044] At block 804, the method 800 continues by plotting a plurality of second activation response levels of the second power transfer coil against the range of driving frequencies. Each of the plurality of second activation response levels can correspond to one of the plurality of coupling coefficients between the first power transfer coil and the second power transfer coil.

[0045] At block 806, the method 800 continues by identifying a pair of one of the plurality of coupling coefficients and a subrange of the range of driving frequencies for which (i) the corresponding first activation response level is above a first threshold level and (ii) the corresponding second activation response level is above a second threshold level. The one of the plurality of coupling coefficients can be about 0, 0.25, 0.5, 0.75, 1, or other value between 0-1 (e.g., 0.9). The first threshold level and the second threshold level can be the same or different. For example, the first threshold level may be about at least 50 mS, 75 mS, 100 mS, 125 mS, 150 mS, etc., while the second threshold level may be about at least 25 mS, 50 mS, 75 mS, 100, mS, etc.

[0046] In some embodiments, the subrange of the range of driving frequencies (i) overlaps with a greater one between a first resonant frequency of the first power transfer coil and a second resonant frequency of the second power transfer coil and/or (ii) does not overlap with a smaller one between a first resonant frequency of the first power transfer coil and a second resonant frequency of the second power transfer coil. For example, the subrange of the range of driving frequencies can be between 10-20 MHz or 12-15 MHz, and/or not between (e.g., outside of) 1-10 MHz or 5-8 MHz.

[0047] At block 808, the method 800 continues by configuring the implantable medical device such that the first power transfer coil and the second power transfer coil have the one of the plurality of coupling coefficients. Configuring the implantable medical device can comprise configuring the first power transfer coil and the second power transfer coil to be substantially coplanar, coaxial, and/or similar in size.

[0048] In some embodiments, the method 800 further includes operating a driving coil within the subrange of the range of driving frequencies while the first power transfer coil and the second power transfer coil have the one of the plurality of coupling coefficients. In some embodiments, operating the driving coil simultaneously activates the first power transfer coil and the second power transfer coil. Activating the first power transfer coil selectively adjusts a geometry of a shunting lumen of the implantable medical device, and/or activating the second power transfer coil charges and/or powers electrical components of the implantable medical device.

Examples

[0049] The present technology is illustrated, for example, according to various aspects described below as numbered examples (1, 2, 3, etc.) for convenience. These are provided as examples and do not limit the present technology. It is noted that any of the dependent examples may be combined in any combination, and placed into a respective independent example. The other examples can be presented in a similar manner.

1. A method of simultaneously powering a first power transfer coil having a first resonant frequency range and a second power transfer coil having a second resonant frequency range different than the first resonant frequency range, wherein the first power transfer coil and the second power transfer coil are implanted within a patient, the method comprising: determining a coupling coefficient between the first power transfer coil and the second power transfer coil; and based at least in part on the determined coupling coefficient, selecting a driving frequency for an external power source that induces (i) a first activation response level in the first power transfer coil above a first threshold, and (ii) a second activation response level in the second power transfer coil above a second threshold, wherein the driving frequency has a frequency value within one, but not both, of the first resonant frequency range or the second resonant frequency range.

2. The method of example 1, further comprising operating a driving coil, positioned adjacent to both the first power transfer coil and the second power transfer coil, at the driving frequency, thereby simultaneously inducing a current in each of the first power transfer coil and the second power transfer coil.

3. The method of example 1 or example 2 wherein the first resonant frequency range is between 10-20 MHz, wherein the second resonant frequency range is between 1-10 MHz, and wherein the frequency value of the driving frequency is within the first resonant frequency range.

4. The method of any of examples 1-3 wherein the first power transfer coil and the second power transfer coil are substantially coplanar.

5. The method of any of examples 1^1 wherein the first power transfer coil and the second power transfer coil are substantially coaxial.

6. The method of any of examples 1-5 wherein the first threshold is about 150 mS, and wherein the second threshold is at least about 50 mS.

7. A method for designing an implantable medical device including a first power transfer coil and a second power transfer coil, the method comprising: plotting a plurality of first activation response levels of the first power transfer coil against a range of driving frequencies, wherein each of the plurality of first activation response levels corresponds to one of a plurality of coupling coefficients between the first power transfer coil and the second power transfer coil; plotting a plurality of second activation response levels of the second power transfer coil against the range of driving frequencies, wherein each of the plurality of second activation response levels corresponds to one of the plurality of coupling coefficients between the first power transfer coil and the second power transfer coil; identifying a pair of one of the plurality of coupling coefficients and a subrange of the range of driving frequencies for which (i) the corresponding first activation response level is above a first threshold level and (ii) the corresponding second activation response level is above a second threshold level; and configuring the implantable medical device such that the first power transfer coil and the second power transfer coil have the one of the plurality of coupling coefficients.

8. The method of example 7 wherein configuring the implantable medical device comprises configuring the first power transfer coil and the second power transfer coil to be substantially coplanar and coaxial.

9. The method of example 7 or example 8 wherein configurating the implantable medical device comprises configuring the first power transfer coil and the second power transfer coil to be substantially similar in size.

10. The method of any of examples 7-9 wherein the one of the plurality of coupling coefficients is about 0.5.

11. The method of any of examples 7-10 wherein the subrange of the range of driving frequencies is between 12-15 MHz.

12. The method of any of examples 7-11 wherein the subrange of the range of driving frequencies is not between 1-10 MHz.

13. The method of any of examples 7-12 wherein the first power transfer coil has a first resonant frequency and the second power transfer coil has a second resonant frequency that is less than the first resonant frequency, and wherein the subrange of the range of driving frequencies overlaps with the first resonant frequency .

14. The method of example 13 wherein the subrange of the range of driving frequencies does not overlap with the second resonant frequency.

15. The method of any of examples 7-14, further comprising operating a driving coil within the subrange of the range of driving frequencies while the first power transfer coil and the second power transfer coil have the one of the plurality of coupling coefficients.

16. The method of example 15 wherein operating the driving coil simultaneously activates the first power transfer coil and the second power transfer coil.

17. The method of example 16 wherein activating the first power transfer coil selectively adjusts a geometry of a shunting lumen of the implantable medical device, and wherein activating the second power transfer coil charges and/or powers electrical components of the implantable medical device.

18. A method for operating an implantable medical device, the method comprising: positioning a driving coil adjacent a first power transfer coil and a second power transfer coil of the implantable medical device, wherein the first and second power transfer coils are substantially coplanar and coaxial, and wherein the first power transfer coil has a first resonant frequency, and wherein the second power transfer coil has a second resonant frequency less than the first resonant frequency; and operating the driving coil at the first resonant frequency, thereby activating the first power transfer coil, wherein activating the first power transfer coil activates the second power transfer such that operating the driving coil at the first resonant frequency simultaneously activates the first and second power transfer coils. 19. The method of example 18 wherein activating the first power transfer coil selectively adjusts a geometry of a shunting lumen of the implantable medical device.

20. The method of example 19 wherein activating the first power transfer coil selectively adjusts the geometry of the shunting lumen via resistive heating.

21. The method of any of examples 18-20 wherein activating the second power transfer coil charges and/or powers electrical components of the implantable medical device.

22. The method of any of examples 18-21, further comprising arranging the first and second power transfer coils relative to one another based, at least in part, on an optimal coupling coefficient between the first and second power transfer coils.

23. The method of example 22, further comprising: generating a first plot of activation response levels of the first power transfer coil at a range of frequencies for a plurality of coupling coefficient values; generating a second plot of activation response levels of the second power transfer coil at the range of frequencies for the plurality of coupling coefficient values; and selecting the optimal coupling coefficient among the plurality of coupling coefficient values based on the generated first plot and the generated second plot.

24. The method of any of examples 18-23 wherein the first resonant frequency is between 10-20 MHz.

25. The method of any of examples 18-24 wherein the second resonant frequency is between 1-10 MHz.

26. An implantable medical device, comprising: a first power transfer coil having a first resonant frequency, wherein the first power transfer coil is configured to be actuated upon receiving radiofrequency energy from an external device at the first resonant frequency; and a second power transfer coil having a second resonant frequency less than the first resonant frequency, wherein the first and second power transfer coils are substantially coplanar and coaxial, and wherein the second power transfer coil is configured to be simultaneously actuated with the first power transfer coil upon receiving radiofrequency energy from the first power transfer coil.

27. The implantable medical device of example 26, further comprising an actuation element operably coupled to the first power transfer coil, wherein the actuation element is configured to be resistively heated upon actuation of the first power transfer coil.

28. The implantable medical device of example 26 or example 27, further comprising one or more electrical components operably coupled to the second power transfer coil, wherein the one or more electrical components are configured to be charged and/or powered upon actuation of the second power transfer coil.

29. The implantable medical device of any of examples 26-28, wherein the first power transfer coil has a first maximum dimension, and wherein the second power transfer coil has a second maximum dimension substantially similar to the first maximum dimension.

Conclusion

[0050] Embodiments of the present disclosure may include some or all of the following components: a battery, supercapacitor, or other suitable power source; a microcontroller, FPGA, ASIC, or other programmable component or system capable of storing and executing software and/or firmware that drives operation of an implant; memory such as RAM or ROM to store data and/or software/firmware associated with an implant and/or its operation; wireless communication hardware such as an antenna system configured to transmit via Bluetooth, WiFi, or other protocols known in the art; energy harvesting means, for example a coil or antenna which is capable of receiving and/or reading an externally-provided signal which may be used to power the device, charge a battery, initiate a reading from a sensor, or for other purposes. Embodiments may also include one or more sensors, such as pressure sensors, impedance sensors, accelerometers, force/strain sensors, temperature sensors, flow sensors, optical sensors, cameras, microphones or other acoustic sensors, ultrasonic sensors, ECG or other cardiac rhythm sensors, SpO2 and other sensors adapted to measure tissue and/or blood gas levels, blood volume sensors, and other sensors known to those who are skilled in the art. Embodiments may include portions that are radiopaque and/or ultrasonically reflective to facilitate image-guided implantation or image guided procedures using techniques such as fluoroscopy, ultrasonography, or other imaging methods. Embodiments of the system may include specialized delivery catheters/systems that are adapted to deliver an implant and/or carry out a procedure. Systems may include components such as guidewires, sheaths, dilators, and multiple delivery catheters. Components may be exchanged via over-the-wire, rapid exchange, combination, or other approaches.

[0051] The above detailed description of embodiments of the technology are not intended to be exhaustive or to limit the technology to the precise forms disclosed above. Although specific embodiments of, and examples for, the technology are described above for illustrative purposes, various equivalent modifications are possible within the scope of the technology as those skilled in the relevant art will recognize. For example, although steps are presented in a given order, alternative embodiments may perfomi steps in a different order. The various embodiments described herein may also be combined to provide further embodiments. For example, although this disclosure has been written to describe devices that are generally described as being used to create a path of fluid communication between the left atrium and the right atrium, it should be appreciated that similar embodiments could be utilized for shunts between other chambers of the heart or for shunts in other regions of the body.

[0052] Unless the context clearly requires otherwise, throughout the description and the examples, the words “comprise,” “comprising,” and the like are to be construed in an inclusive sense, as opposed to an exclusive or exhaustive sense; that is to say, in the sense of “including, but not limited to.” As used herein, the terms “connected,” “coupled,” or any variant thereof, means any connection or coupling, either direct or indirect, between two or more elements; the coupling of connection between the elements can be physical, logical, or a combination thereof. Additionally, the words “herein,” “above,” “below,” and words of similar import, when used in this application, shall refer to this application as a whole and not to any particular portions of this application. Where the context permits, words in the above Detailed Description using the singular or plural number may also include the plural or singular number respectively. As used herein, the phrase “and/or” as in “A and/or B” refers to A alone, B alone, and A and B. Additionally, the term “comprising” is used throughout to mean including at least the recited feature(s) such that any greater number of the same feature and/or additional types of other features are not precluded. It will also be appreciated that specific embodiments have been described herein for purposes of illustration, but that various modifications may be made without deviating from the technology. Further, while advantages associated with some embodiments of the technology have been described in the context of those embodiments, other embodiments may also exhibit such advantages, and not all embodiments need necessarily exhibit such advantages to fall within the scope of the technology. Accordingly, the disclosure and associated technology can encompass other embodiments not expressly shown or described herein.

Claims

CLAIMS What is claimed is:

2. The method of claim 1, further comprising operating a driving coil, positioned adjacent to both the first power transfer coil and the second power transfer coil, at the driving frequency, thereby simultaneously inducing a current in each of the first power transfer coil and the second power transfer coil.

3. The method of claim 1 wherein the first resonant frequency range is between 10-20 MHz, wherein the second resonant frequency range is between 1-10 MHz, and wherein the frequency value of the driving frequency is within the first resonant frequency range.

4. The method of claim 1 wherein the first power transfer coil and the second power transfer coil are substantially coplanar.

5. The method of claim 1 wherein the first power transfer coil and the second power transfer coil are substantially coaxial.

6. The method of claim 1 wherein the first threshold is about 150 mS, and wherein the second threshold is at least about 50 mS.

8. The method of claim 7 wherein configuring the implantable medical device comprises configuring the first power transfer coil and the second power transfer coil to be substantially coplanar and coaxial.

9. The method of claim 7 wherein configurating the implantable medical device comprises configuring the first power transfer coil and the second power transfer coil to be substantially similar in size.

10. The method of claim 7 wherein the one of the plurality of coupling coefficients is about 0.5.

11. The method of claim 7 wherein the subrange of the range of driving frequencies is between 12-15 MHz.

12. The method of claim 7 wherein the subrange of the range of driving frequencies is not between 1-10 MHz.

13. The method of claim 7 wherein the first power transfer coil has a first resonant frequency and the second power transfer coil has a second resonant frequency that is less than the first resonant frequency, and wherein the subrange of the range of driving frequencies overlaps with the first resonant frequency .

14. The method of claim 13 wherein the subrange of the range of driving frequencies does not overlap with the second resonant frequency.

15. The method of claim 7, further comprising operating a driving coil within the subrange of the range of driving frequencies while the first power transfer coil and the second power transfer coil have the one of the plurality of coupling coefficients.

16. The method of claim 15 wherein operating the driving coil simultaneously activates the first power transfer coil and the second power transfer coil.

17. The method of claim 16 wherein activating the first power transfer coil selectively adjusts a geometry of a shunting lumen of the implantable medical device, and wherein activating the second power transfer coil charges and/or powers electrical components of the implantable medical device.

18. A method for operating an implantable medical device, the method comprising: positioning a driving coil adjacent a first power transfer coil and a second power transfer coil of the implantable medical device, wherein the first and second power transfer coils are substantially coplanar and coaxial, and wherein the first power transfer coil has a first resonant frequency, and wherein the second power transfer coil has a second resonant frequency less than the first resonant frequency; and operating the driving coil at the first resonant frequency, thereby activating the first power transfer coil, wherein activating the first power transfer coil activates the second power transfer such that operating the driving coil at the first resonant frequency simultaneously activates the first and second power transfer coils.

19. The method of claim 18 wherein activating the first power transfer coil selectively adjusts a geometry of a shunting lumen of the implantable medical device.

20. The method of claim 19 wherein activating the first power transfer coil selectively adjusts the geometry of the shunting lumen via resistive heating.

21. The method of claim 18 wherein activating the second power transfer coil charges and/or powers electrical components of the implantable medical device.

22. The method of claim 18, further comprising arranging the first and second power transfer coils relative to one another based, at least in part, on an optimal coupling coefficient between the first and second power transfer coils.

23. The method of claim 22, further comprising: generating a first plot of activation response levels of the first power transfer coil at a range of frequencies for a plurality of coupling coefficient values; generating a second plot of activation response levels of the second power transfer coil at the range of frequencies for the plurality of coupling coefficient values; and selecting the optimal coupling coefficient among the plurality of coupling coefficient values based on the generated first plot and the generated second plot.

24. The method of claim 18 wherein the first resonant frequency is between 10-20 MHz.

25. The method of claim 18 wherein the second resonant frequency is between 1-10 MHz.