Patent Grant
11432874
This disclosure is generally related to percutaneous cardiac surgery, and more particularly to percutaneously deployed medical devices suitable for determining locations of cardiac features and/or ablating regions of cardiac tissue.
Cardiac surgery was initially undertaken only by performing a sternotomy, a type of incision in the center of the chest, that separates the sternum (chestbone) to allow access to the heart. In the previous several decades, more and more cardiac operations are performed using percutaneous techniques, that is medical procedures where access to inner organs or other tissue is gained via a catheter.
Percutaneous surgeries benefit patients by reducing surgery risk, complications and recovery time. However, the use of percutaneous technologies also raises some particular challenges. Medical devices used in percutaneous surgery need to be deployed via narrow tubes called catheter sheaths, which significantly increase the complexity of the device structure. As well, doctors do not have direct visual contact with the medical tools used once they are placed within the body, and positioning the tools correctly and operating the tools successfully can often be very challenging.
One example of where percutaneous medical techniques are starting to be used is in the treatment of a heart disorder called atrial fibrillation. Atrial fibrillation is a disorder in which spurious electrical signals cause an irregular heart beat. Atrial fibrillation has been treated successfully in open heart methods using a technique know as the “Maze procedure”. During this procedure, doctors create lesions in a specific pattern in the left and right atriums that eliminate the spurious electrical signals. Such lesions were originally created using incisions, but are now typically created by ablating the tissue with RF energy. The procedure is performed with a high success rate under direct vision, but is relatively complex to perform percutaneously because of the difficulty in creating the lesions in the correct spots. Substantial problems, potentially leading to severe adverse results, may occur if the lesions are placed incorrectly.
Key factors which are needed to dramatically improve the percutaneous treatment of atrial fibrillation are enhanced methods for deployment, positioning, and operation of the treatment device. It is particularly important to know the position of the elements which will be creating the lesions relative to cardiac features such as the pulmonary veins and mitral valve.
Several methods have been previously developed for positioning percutaneously deployed medical devices with the heart. However, there are significant challenges associated with each of these methods. One method is to map the inside of the atrium by sensing electrical activity on the atrium wall. Devices that use such a method require intimate electrical contact with the atrium wall which is not always possible because of scar tissue and deposits. Also, such devices fail to accurately map the edges of the openings where the veins enter the atrium, which is important for correct placement of the ablation pattern. Other methods, such as using an array of ultrasonic transducers, are not practical as devices that make use of such methods will not fit through a catheter of a reasonable size (6-8 mm diameter). Yet another method for positioning the treatment device is to make use of an external system for providing navigation, such as a magnetic positioning system. These systems are very expensive and have difficulty delivering the resolution and accuracy needed for correct placement of ablation.
Atrial fibrillation is but one example of a cardiac surgery that requires improved navigation and deployment for percutaneous treatment. There are many others that require similar improvement, such as mitral valve repair.
Thus, there is a need for methods and apparatus that improve navigation and percutaneous deployment of medical devices, as well as determination of the relative position of cardiac features such as pulmonary veins and the mitral valve with respect to a medical device. There is a further need for methods and apparatus that allow the formation of lesions in a specified position relative to cardiac features such as pulmonary veins and the mitral valve.
The present design of a medical device with enhanced capabilities for deployment, positioning and ablating within the heart employs a method for distinguishing tissue from blood and may be used to deliver superior positional information of the device relative to ports in the atrium, such as the pulmonary veins and mitral valve. The device may employ methods such as blood flow detection, impedance change detection or deflection force detection to discriminate between blood and tissue. The device may also improve ablation positioning and performance by using the same elements for discriminating between blood and tissue as are used for ablation. Other advantages will become apparent from the teaching herein to those of skill in the art.
At least one embodiment may be summarized as a method of operating a medical system including sensing at least one characteristic by each of a number of transducer elements carried by a device located in at least a portion of a bodily organ, the at least one characteristic indicative of at least one of a presence of a fluid (e.g., blood) and a presence of non-fluid tissue (e.g., wall of heart); computationally discriminating between the fluid and the non-fluid tissue based at least in part on the at least one characteristic sensed by at least some of the transducer elements; and providing information indicative of at least a position of the device in the bodily organ based on the computational discrimination between the fluid and the non-fluid tissue.
The method may further include ablating a portion of the non-fluid tissue in a bodily organ, for example the heart. The method may further include sensing an electrical potential of the non-blood tissue in the heart at least once after the ablating; and producing an indication based on the sensed electrical potential of the non-blood tissue indicative of whether the ablating was successful. Sensing at least one characteristic by each of a number of transducer elements may include sensing a permittivity of the fluid or the non-fluid tissue at each of a plurality of frequencies. Sensing at least one characteristic by each of a number of transducer elements may include sensing a force exerted on the sensor by the fluid or non-fluid tissue. Providing information indicative of at least a position of the device in the bodily organ based on the computational discrimination between the fluid and the non-fluid tissue may include providing information indicative of a three-dimensional pose of the device with respect to at least the portion of a heart. The method may further include intravascularly guiding the device to a desired position while at least a portion of the device is in an unexpanded configuration; selectively moving at least the portion of the device into an expanded configuration to position the transducer elements at least proximate the non-fluid tissue; selectively moving at least the portion of the device into the unexpanded configuration; and intravascularly retrieving the device from the desired position while at least a portion of the device is in the unexpanded configuration.
At least one embodiment may be summarized as a medical system including a device positionable in at least a portion of a bodily organ (e.g., a heart), the device including a plurality of transducer elements, at least some of the transducer elements responsive to at least one characteristic indicative of a presence of either a fluid (e.g., blood) or non-fluid tissue (e.g., wall of heart) a computing system having at least one processor and at least one memory that stores instructions, the computing system configured to computationally discriminate between the fluid and the non-fluid tissue based at least in part on the at least one characteristic sensed by at least some of the transducer elements; and at least one transducer configured to provide information indicative of at least a position of the device in the bodily organ based on the computational discrimination between the fluid and the non-fluid tissue.
The system may further include an ablation source, wherein at least some of the transducer elements may be coupled to an ablation source and selectively operable to ablate a portion of the non-fluid tissue in the heart. At least some of the transducer elements that are responsive to at least one characteristic indicative of a presence of either the fluid or the non-fluid tissue in the bodily organ may also be responsive to electrical potential of the non-fluid tissue. At least some of the transducer elements may be responsive to electrical potentials of the non-fluid tissue, and the computing system may be further configured to produce an indication indicative of whether the ablation was successful based on at least one sensed electrical potential of the non-fluid tissue. At least a portion of the device may be selectively moveable between an unexpanded configuration and an expanded configuration, the device sized to be delivered intravascularly when at least the portion of the device is in the unexpanded configuration, and the transducer elements positioned sufficient proximate the non-fluid tissue to sense the at least one characteristic in the expanded configuration. The system may further include a catheter having a proximal end and a distal end opposed to the proximal end, the device coupled to the catheter at the distal end thereof; at least one communications path communicatively coupling the transducer elements and the computing system, the communications path including a multiplexer and a demultiplexer, the multiplexer on a computing system side of the communications path and the demultiplexer on a device side of the communications path.
At least one embodiment may be summarized as a method of operating a device in at least a portion of a heart, including sensing at least one characteristic by each of a number of transducer elements carried by the device located in at least the portion of the heart, the at least one characteristic indicative of at least one of a presence of blood and a presence of non-blood tissue; computationally discriminating between the blood and the non-blood tissue based at least in part on the at least one characteristic sensed by at least some of the transducer elements; providing information indicative of a position of the device in the heart based on the discrimination between the blood and the non-blood tissue; sensing an electrical potential of the non-blood tissue in the heart; and providing an indication based on the sensed electrical potential of the non-blood tissue.
The method may further include ablating a portion of the tissue in the heart, wherein sensing an electrical potential of the non-blood tissue in the heart may occur at least once after the ablating. The method may further include evaluating the sensed electrical potential of the non-blood tissue in the heart to determine whether the ablating was successful.
At least one embodiment may be summarized as a medical system including a device positionable in at least a portion of a heart, the device including a plurality of transducer elements at least some of the transducer elements responsive to at least one characteristic indicative of at least one of a presence of blood and a presence of non-blood tissue and at least some of the transducer elements responsive to an electrical potential of the non-blood tissue in the heart; a computing system having at least one processor and at least one memory that stores instructions, the computing system configured to computationally discriminate between the blood and the non-blood tissue based at least in part on the at least one characteristic sensed by at least some of the transducer elements; and at least one transducer configured to provide information indicative of a position of the device in the heart based on the computational discrimination between the blood and the non-blood tissue and provide an indication based on the sensed electrical potential of the non-blood tissue.
The system may further include an ablation source, wherein at least some of the transducer elements may be coupled to an ablation source and selectively operable to ablate a portion of the non-blood tissue in the heart. The system may further include a switch operable to selectively couple the transducer elements between an ablation mode and a sense mode, where the transducer elements may ablate the non-blood tissue in the ablation mode and may sense the at least one characteristic in the sense mode. At least some of the transducer elements that are responsive to at least one characteristic indicative of a presence of either blood or non-blood tissue may also be responsive to electrical potential of the non-blood tissue. At least a portion of the device may be selectively moveable between an unexpanded configuration and an expanded configuration, the device sized to be delivered intravascularly when at least the portion of the device is in the unexpanded configuration, and the device sized to position the transducer elements sufficiently proximate the non-blood tissue to sense the at least one characteristic in the expanded configuration. The transducer elements may include at least one of a conductive trace on a flexible electrically insulative substrate, a conductive wire, a conductive tube, a carbon fiber material and a polymeric piezoelectric material. The device may include a number of flexible electrically insulative substrates that deform between an unexpanded configuration and an expanded configuration.
At least one embodiment may be summarized as a device to be inserted intravascularly, including a shaft moveable with respect to a catheter member; at least a first helical member configured to move between a radially unexpanded configuration and a radially expanded configuration in response to the movement of the shaft with respect to the catheter, the device sized to be delivered intravascularly when at least the first helical member is in the unexpanded configuration; and a plurality of transducer elements that move in response to the movement of the first helical member between the radially unexpanded configuration and the radially expanded configuration, at least some of the transducer elements responsive to a characteristic of at least one of a fluid and a non-fluid tissue.
The device may further include at least a second helical member configured to move between a radially unexpanded configuration and a radially expanded configuration in response to the movement of the shaft with respect to the catheter. The first helical member may carry some of the transducer elements and the second helical member may carry some of the transducer elements. The first helical member may be disposed radially spaced about the shaft. The first helical member may be wound in one of a clockwise or a counterclockwise orientation with respect to the shaft and the second helical member may be wound in the other of the clockwise or the counterclockwise orientation with respect to the shaft. The device may further include a number of elongated ribs physically coupled between a proximate and a distal end of the first helical member. The elongated ribs may each form a respective flexible electrically insulative substrate and at least some of the transducer elements may comprise respective electrically conductive traces carried by the flexible electrically insulative substrate. The shaft may be axially moveable with respect to the catheter member between an extended position and a withdrawn position, a distal end of the shaft spaced relatively closer to an end of the catheter member in the withdrawn position than in the extended position, where the first helical member is in the unexpanded configuration when the shaft is in the extended position and is in the expanded configuration when the shaft is in the withdrawn position. The shaft may be rotatably moveable with respect to the catheter member between an extended position and a withdrawn position, a distal end of the shaft spaced relatively closer to an end of the catheter member in the withdrawn position than in the extended position, where the first helical member is in the unexpanded configuration when the shaft is in the extended position and is in the expanded configuration when the shaft is in the withdrawn position. The shaft may extend at least partially through a lumen of the catheter member to allow manipulation of the device from a position externally located from a patient. At least some of the transducer elements may be responsive to convective cooling from a flow of blood over the transducer elements. At least some of the transducer elements may be responsive to a permittivity at each of a plurality of frequencies. At least some of the transducer elements may be responsive to a force. At least some of the transducer elements may comprise a polymeric piezoelectric material. At least some of the transducer elements may be responsive to an electrical potential of a portion of the non-blood tissue. At least some of the transducer elements may include an electrically conductive trace carried by a flexible electrically insulative substrate. The first helical member may form a flexible electrically insulative substrate and at least some of the transducer elements may comprise respective electrically conductive traces carried by the flexible electrically insulative substrate. At least some of the transducer elements may include an electrically conductive wire. At least some of the transducer elements may include an electrically conductive tube. At least some of the transducer elements may include an electrically conductive carbon fiber.
At least one embodiment may be summarized as a method of operating a device including at least a first helical member and a plurality of transducer elements that are responsive to at least one characteristic of non-blood tissue, comprising: guiding a device in an unexpanded configuration intravascularly to a desired position; and expanding at least the first helical member of the device into an expanded configuration such that the plurality of transducer elements are positioned to sense the at least one characteristic over a substantial portion of the non-blood tissue.
The expanding at least the first helical member may include axially moving a shaft that extends at least partially through a lumen of a catheter member in a first direction. The expanding at least first helical member may include rotatably moving a shaft that extends at least partially through a lumen of a catheter member in a first direction. The method may further include retracting at least the first helical member into the unexpanded configuration; and intravascularly guiding the device in the unexpanded configuration to remove the device. The retracting at least the first helical member into the unexpanded configuration may include at least one of axially or radially moving the shaft that extends at least partially through the lumen of the catheter member in an opposite direction than moved when expanded.
At least one embodiment may be summarized as a medical device, including at least a first inflatable member having at least one chamber and at least one port that provides fluid communication with the chamber, the first inflatable member configured to move between an unexpanded configuration and an expanded configuration in response to a change of a pressure in the chamber, the device sized to be delivered intravascularly when at least the first inflatable member is in the unexpanded configuration; a plurality of transducer elements that move in response to the movement of the first inflatable member between the radially unexpanded configuration and the radially expanded configuration, at least some of the transducer elements responsive to a characteristic of at least one of a fluid and a non-fluid tissue.
The first inflatable member may have at least one passage that provides fluid communication across the first inflatable member. The at least one passage may provide fluid communication between an upstream position and a downstream position with respect to a position of the inflatable member when positioned in a cardiovascular structure. The at least one passage may be formed by a reinforced portion of the first inflatable member. The reinforced portion of the first inflatable member may include at least a rib, an elastic member, and a thickened portion of a wall that forms the passage. The port may be coupled to a lumen of a catheter member to allow fluid communication with the chamber from a fluid reservoir that is externally located with respect to a patient. At least some of the transducer elements may be responsive to convective cooling from a flow of blood over the transducer elements. At least some of the transducer elements may be responsive to a permittivity at each of a plurality of frequencies. At least some of the transducer elements may be responsive to a force. At least some of the transducer elements may comprise a polymeric piezoelectric material. At least some of the transducer elements may be responsive to an electrical potential of a portion of the non-blood tissue. At least some of the transducer elements may include an electrically conductive trace carried by a flexible electrically insulative substrate. The first helical member may form a flexible electrically insulative substrate and at least some of the transducer elements may comprise respective electrically conductive traces carried by the flexible electrically insulative substrate. At least some of the transducer elements may include an electrically conductive wire. At least some of the transducer elements may include an electrically conductive tube. At least some of the transducer elements may include an electrically conductive carbon fiber.
At least one embodiment may be summarized as a method of operating a device including at least a first inflatable member and a plurality of transducer elements that are responsive to at least one characteristic of non-blood tissue, comprising: guiding a device in an unexpanded configuration intravascularly to a desired position; and inflating at least the first inflatable member of the device into an expanded configuration such that the plurality of transducer elements are positioned to sense the at least one characteristic over a substantial portion of the non-blood tissue.
Inflating at least the first helical member may include providing a fluid to a chamber of the first inflatable member through a lumen of a catheter member. The method may further include deflating at least the first inflatable member into the unexpanded configuration; and intravascularly guiding the device in the unexpanded configuration to remove the device. Deflating at least the first helical member into the unexpanded configuration may include removing the fluid from the chamber through the lumen of the catheter member.
In the drawings, identical reference numbers identify similar elements or acts. The sizes and relative positions of elements in the drawings are not necessarily drawn to scale. For example, the shapes of various elements and angles are not drawn to scale, and some of these elements are arbitrarily enlarged and positioned to improve drawing legibility. Further, the particular shapes of the elements as drawn, are not intended to convey any information regarding the actual shape of the particular elements, and have been solely selected for ease of recognition in the drawings.
In the following description, certain specific details are set forth in order to provide a thorough understanding of various embodiments of the invention. However, one skilled in the art will understand that the invention may be practiced without these details. In other instances, well-known structures associated with RF ablation and electronic controls such as multiplexers have not been shown or described in detail to avoid unnecessarily obscuring descriptions of the embodiments of the invention.
Unless the context requires otherwise, throughout the specification and claims which follow, the word “comprise” and variations thereof, such as, “comprises” and “comprising” are to be construed in an open, inclusive sense, that is as “including, but not limited to.”
The word “ablation” should be understood to mean any disruption to certain properties of the tissue. Most commonly the disruption is to the electrical conductivity and is achieved by heating, which could be either resistive or by use of Radio Frequencies (RF). Other properties, such as mechanical, and other means of disruption, such as optical, are included when the term “ablation” is used.
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 invention. 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, structures, or characteristics may be combined in any suitable manner in one or more embodiments.
As used in this specification and the appended claims, the singular forms “a,” “an,” and “the” include plural referents unless the content clearly dictates otherwise. It should also be noted that the term “or” is generally employed in its sense including “and/or” unless the content clearly dictates otherwise.
The headings provided herein are for convenience only and do not interpret the scope or meaning of the claimed invention.
Overview of Device and Mapping Methods
Various embodiments of percutaneously or intravascularly deployed medical devices are described herein. The medical devices are capable of expanding into a cavity within a body and sensing characteristics (e.g., convective cooling, permittivity, force) that distinguish between blood and non-blood tissue. Such sensed characteristic allow a medical system to map the cavity, for example using positions of openings or ports into and out of the cavity to determine a position and/or orientation (i.e., pose) of the medical device in the cavity. The medical devices may also be capable of ablating tissue in a desired pattern within the cavity. The medical devices may further be capable of sensing characteristics (e.g., electrical activity), indicative of whether ablation has been successful.
An example of the mapping performed by the medical treatment devices would be to locate the position of the four openings leading to the pulmonary veins as well as the mitral valve on the interior surface of the left atrium. The mapping is based on locating such openings by differentiating between blood and non-blood tissue. There are many ways to differentiate non-blood tissue from a liquid such as blood or to differentiate non-blood tissue from an opening in case a liquid is not present. By the way of example, three approaches will be detailed in the disclosure:
1. One approach to determining the locations is to use the convective cooling of heated transducer elements by the blood. A slightly heated mesh of transducer elements positioned adjacent to the non-blood tissue that forms walls of the atrium and across the openings or ports of the atrium will be cooler at the areas which are spanning the openings or ports carrying blood flow.
2. Another approach to determining the locations is to make use of the differing change in dielectric constant as a function of frequency between blood and non-blood tissue. A set of transducer elements positioned around the non-blood tissue that forms the interior surface of the atrium and across the openings or ports of the atrium monitor the ratio of the dielectric constant from 1 KHz to 100 KHz. Such can be used to determine which of those transducer elements are not proximate to non-blood tissue, which is indicative of the locations of openings or ports.
3. Yet another approach to determining the locations is to sense a position of the non-blood tissue that forms the atrium walls using transducer elements that sense force (i.e., force sensors). A set of force detection transducer elements positioned around the non-blood tissue that forms the interior surface of the atrium and across the openings or ports of the atrium can be used to determine which of the transducer elements are not in contact with the non-blood tissue, which is indicative of the locations of openings or ports.
The medical device 100 may be percutaneously and/or intravascularly inserted into a portion of the heart 102, for example in a left atrium 104 of the heart 102. In this example, the medical device is delivered via a catheter 106 inserted via the superior vena cava 108 and penetrating the transatrial septum 110 from a right atrium 112.
The catheter 106 may include one or more lumens 114. The lumen(s) 114 may carry one or more communications and/or power paths, for example one or more wires 116. The wires 116 provide connections to the medical device 100 that are accessible externally from a patient in which the medical device 100 is inserted.
As discussed in more detail herein, the medical device 100 comprises a frame 118 which expands (shown in expanded configuration in
The medical device 200 takes the form of an expandable electrode grid or array 202, including a plurality of flexible strips 204 (three called out in
The expandable frame 208, as well as flexible strips 204 can be delivered and retrieved via a catheter member, for example a catheter sheath introducer 210, which in some embodiments may have a diameter of about 8 mm or smaller. Flexible strips 204 may be made of one or more thin layers of Kapton (polyimide), for instance 0.1 mm thick. Transducer elements (e.g., electrodes and/or sensors) 206 may be built on the flexible strips 204 using standard printed circuit board processes. An overlay of a thin electrical insulation layer (e.g., Kapton about 10-20 microns thick) may be used to provide electrical insulation, except in areas needing electrical contact to blood and non-blood tissue. In some embodiments, the flexible strips 204 can form an elongated cable 216 of control leads 218, for example by stacking multiple layers, and terminating in a connector 220. The electrode grid or array 202 is typically disposable.
The medical device 200 may communicate with, receive power from and/or be controlled by a control system 222. The control system 222 may include a computing system 224 having one or more processors 226 and one or more memories 228 that store instructions that are executable by the processors 226 to process information received from the medical device 200 and/or to control operation of the medical device 200, for example activating selected transducer elements 206 to ablate non-blood tissue. The control system 222 may include an ablation source 230. The ablation source 230 may, for example, provide electrical power, light or low temperature fluid to the selected transducer elements to cause ablation. The control system 222 may also include one or more user interface or input/output (I/O) devices, for example one or more displays 232, speakers 234, keyboards, mice, joysticks, track pads, touch screens or other transducers to transfer information to and from a user, for example a care provider such as a medical doctor or technician. For example output from the mapping process may be displayed on a display 232.
While the disclosed systems are described with examples of cardiac mapping, the same or similar systems may be used for mapping other bodily organs, for example gastric mapping, bladder mapping, arterial mapping and mapping of any lumen or cavity into which the medical device 204 may be introduced.
The term “transducer element” in this disclosure should be interpreted broadly as any component capable of distinguishing between blood and tissue, sensing temperature, creating heat, ablating tissue and measuring electrical activity of a non-blood tissue surface, or any combination thereof. A transducer element may be constructed from several parts, which may be discrete components or may be integrally formed.
Sensing Convective Cooling
The portion of the medical device 300 is particularly suitable to sense convective cooling. The medical device 300 includes miniature transducer elements 302a, 302b, 302c (collectively 302) capable of producing heat. The transducer elements 302 may, for example, be made of insulated resistive wire, such as Nickel, or Nickel-iron composition. The resistive wire may be mounted on an expandable frame 304. In this embodiment, the expandable frame 304 may also be made of a material that has high impedance. Current passed through each transducer element 302 raises the temperature of the transducer element 302 by a nominal amount. A rise of 0.5-3.0 degrees Celsius above normal blood temperature has been found to be sufficient in most cases. The power required to raise the temperature in this particular embodiment is about 10-50 mW per transducer element 302. A central one of the transducer elements 302b, which is placed across the opening, port of ostium 306 of the pulmonary vein 308 will be cooled by blood flow more than the neighboring transducer elements 302a, 302c which are adjacent to the inner or interior surface or non-blood tissue 310 that forms the wall of the heart. Transducer elements 302 which are found to be cooler on expandable frame 304 indicate the locations of openings or ports 306 in the non-blood tissue 310 that forms the wall of the heart. This embodiment does not require intimate contact with the bodily tissue 310 of the heart wall, as even a few millimetres from the openings or ports 306 the cooling effect is significant compared to the cooling effect a few millimetres from the non-blood tissue 310 of the heart wall. The back side of the transducer elements 302 may be thermally insulated for improved performance of both sensing and ablation. Using a flat ribbon for the expandable frame 304 may be advantageous. A cross section of a ribbon expandable frame 304 may, for example have dimensions of 0.2×2 mm for stainless steel or 0.3×2.5 mm for Nitinol. The insulation on the back side of the transducer elements 302 may take the form of a coat of silicone rubber.
If the transducer elements 302 are made of a material that has a significant change in resistance with temperature, the temperature drop can be determined from the resistance of the transducer element 302. The resistance can be determined by measuring the voltage across the transducer element 302 for a given current, or alternatively by measuring the current across the transducer element 302 for a given voltage, for example via a Wheatstone bridge circuit. Thus, some embodiments may take advantage of convective cooling by the flow of blood, at least some of the transducer elements 302 functioning as a hot wire anemometer. Nickel wire is a suitable material to use, as nickel is inert, highly resistive and has a significant temperature coefficient of resistance (about 0.6% per deg C.). Since the resistance of the transducer elements 302 is low (typically less than 5 ohm), the electrical noise is very low and temperature changes as low as 0.1-1 deg can be detected. There are several techniques to improve on this sensitivity. One method is to sample the voltage waveform in synchronization with the heart rate. Another is to remove the average voltage via AC coupling and only amplify the voltage change or derivative. Yet another method to reduce the electrical noise is to pass the signal through a digital band pass filter having a center frequency tracking the heart rate.
A combined sensor and ablation transducer element 408 that can be used for both sensing flow and ablating can be made using standard PCB construction processes. For example, a 2-4 mil copper trace on a Kapton® substrate can be used. Copper changes resistance sufficiently with temperature to be used to determine blood flow in the manner discussed above. Copper can also be used as an ablation element by applying sufficient current through the copper to cause the combined sensor and ablation transducer element 408 to heat resistively, for example to a temperature above 60° C. Power in the range of approximately 130-250 mW delivered to a copper pattern that has external dimensions of 3 mm×10 mm and is thermally insulated on the side away from the non-blood tissue may be sufficient to transmurally ablate a 3 ram deep section of the non-blood tissue that forms the atrium wall. In this approach, the non-blood tissue is heated by conduction from the copper combined sensor and ablation transducer element 408. When heating the non-blood tissue by conduction, the combined sensor and ablation transducer element 408 may be electrically insulated from the non-blood tissue.
Alternatively, the combined sensor and ablation transducer element 408 can also be used to ablate non-blood tissue by using the combined sensor and ablation transducer element 408 as an electrode for delivering RF energy to the non-blood tissue. In this scenario, electrical current is transferred directly to the non-blood tissue and the non-blood tissue is resistively heated by the current flow. When delivering RF energy, a preferred method may be to have low electrical impedance between the combined sensor and ablation transducer element 408 and the non-blood tissue. Delivering RF energy is also possible if the combined sensor and ablation transducer element 408 is capacitively coupled to the non-blood tissue, so long as the impedance at the frequency of RF energy being used is sufficiently low—typically under a few kilo ohms or less for a combined sensor and ablation transducer element of the size mentioned above. Note that in the case where the combined sensor and ablation transducer element 408 has a low electrical impedance connection to the non-blood tissue for low frequencies, it is also possible to use the combined sensor and ablation transducer element 408 to sense an electrical potential in the non-blood tissue that forms the heart wall, for example to generate an electro-cardiogram. Thus it is possible for the same combined sensor and ablation transducer element 408 to sense flow, sense electrical potential of the non-blood tissue that forms the heart wall, and ablate non-blood tissue.
To cause the transducer element 420b to heat to a temperature sufficient to cause ablation, while not causing ablation at transducer element 420a and transducer element 420c:
For example, if the voltages at lead 422c and lead 422d are set to 0 v, voltage at lead 422b is set to n volts and voltage at lead 422a is set to % n volts, the power delivered to the transducer element 420a will be only 11% of that delivered to the transducer element 420b. This technique of having adjacent transducer elements 420 share common leads 422 can, for example, be used in a elongated one-dimensional line of connected transducer elements 420 or may be applied to transducer elements 420 connected in two-dimensional (as illustrated in
There are other approaches for creating the transducer elements that do not rely on a PCB.
The structures of the embodiments of
In this example, transducer elements 702a-702d (collectively 702) may be resistive elements, for example formed from copper traces on a flexible printed circuit board substrate, or resistive wires mounted on a structure. Each transducer element 702 is connected by electronic transducer selection switches 704a-704h (collectively 704) to a single pair of wires 706a, 706b (collectively 706) that provide a path out of the body via a cable 708. The transducer selection switches 704 may, for example be FET or MOSFET type transistors. The transducer selection switches 704 will typically need to carry significant power during the ablation phase. The cable 708 may extend through a lumen of a catheter or may otherwise form part of a catheter structure.
The transducer selection switches 704 are selected by signals applied by a demultiplexer (selector) 710. The demultiplexer 710 may be controlled by a small number of wires 712 (or even a single wire if data is relayed in serial form). The wires 706, 712 extend out of the body via the cable 708. The transducer selection switches 704 and the demultiplexer 710 may be built into a catheter (e.g., catheter 106 of
At the other or proximate end of the catheter are a mode selection switch 726 and multiplexer 714. The mode selection switch 726 is operable to select between a flow sensing mode (position shown in the drawing) and an ablation mode (second position of the mode selection switch 726). In flow sensing mode, a current is created by a voltage source 716 and resistor 718 (forming an approximate current source) and routed into a transducer element 702 selected via transducer selection switches 704. The two transducer selection switches 704 that are connected to a given one of the transducer elements 702 to be used to sense flow, are set to be closed and the remainder of the transducer selection switches 704 are set to be open. The voltage drop across the transducer element 702 is measured via an Analog-to-Digital converter (ADC) 720 and fed to the control computer 722.
It may be advantageous to use alternating current or a combination of alternating current and direct current for sensing and ablation. For example, direct current for ablation and alternating current for sensing. Alternating current approaches may also prevent errors from electrochemical potentials which could be significant if different metals come in touch with blood.
Determination of the location of the openings or ports into the chamber may be achieved by turning on all of transducer elements 702 sequentially or in groups and determining a temperature by measuring the resistance of each transducer element 702. A map of the temperature of the transducer elements 702 may be formed in control computer 722 or the control computer 722 may otherwise determine a position and/or orientation or pose of the device in the cavity. The transducer elements 702 with lower temperatures correspond to the openings or ports leading to the veins or valves.
When mode selection switch 726 is set to select ablation, an ablation power source 724 is connected sequentially to the transducer elements 702 that are selected by the control computer 722 by addressing the multiplexer 714, which in turn controls the transducer selection switches 704 via the demultiplexer 710. The ablation power source 724 may be an RF generator, or it may be one of several other power sources, several of which are described below. If ablation power source 710 is an RF generator, the configuration of
During ablation it may be desirable to monitor the temperature of the non-blood tissue. The ideal temperature range for the non-blood tissue during ablation is typically 50-100° C. Since the example includes temperature monitoring as part of the blood flow sensing, the progress of ablation can be monitored by temporarily switching mode selection switch 726 to a temperature sensing position several times during the ablation.
In this example, transducer elements 802a-802g (collectively 802, only seven called out in
The control wires 806 may be coupled to respective ones of transducer selection switches 810a-810i (collectively 810) at a proximate end of a catheter. Each of the transducer selection switches 810 is controlled by a control system 812, which may, for example, take the form of a programmed general purpose computer, special purpose computer, applications specific integrated circuit (ASIC) or field programmable gate array (FPGA). The control system 812 applies signals to select between an adjustable current source 814a-814i (collectively 814) and ground 816 (only one called out in
When a given transducer element 802 is to be used for blood flow sensing, the transducer selection switch 810 connected to the node A-I on one end of the given transducer element 802 is set to select the current source 814 and the transducer selection switch 810 connected to the node on the other end of the given transducer element 802 is configured to select ground 816. All nodes connected by a transducer element 802 to the node configured to select a current source 814 are also configured to select a current source 814. All nodes connected by a transducer element 802 to the node configured to select a ground are also configured to select ground 816. All of the connected current sources 814 are adjusted to deliver the same small voltage at the nodes A-I they are connected to. For example, if the transducer element 802e is to be used, then nodes B, D E, and H will be connected to current sources 814b, 814d, 814e, 814h, and nodes A, C, F, G, and I will be connected to ground 816. The connected current sources 814b, 814e, 814d, 814h will be adjusted so that the voltage at nodes B, E, D, and H will be the same. The control system 812 controls the voltage at the nodes, for example by:
In this configuration, the current through all transducer elements 802 connected to the given transducer element 802e will be zero. Therefore all current from the current source 814e connected to the given transducer element 802e will pass through the transducer element 802e. As both the voltage drop across and the current through the given transducer element 802e are known, the resistance can be determined and the corresponding temperature can be determined. Determination of the location of the openings or ports into the cavity (e.g., chamber or atrium) may be achieved by turning on all or at least some of transducer elements 802 sequentially, and determining the temperature by measuring a resistance of each of the transducer elements 802. The control system 812, or some other system, may produce a map of the temperature of the transducer elements 802, where the lower temperatures correspond to the openings or ports leading to veins or valves.
When a transducer element 802 is to be used for ablation, the transducer selection switch 810 connected to the node A-I on one end of the given transducer element 802 is set to select the current source 814 and the transducer selection switch 810 connected to the node A-I on the other end of the given transducer element 802 is configured to select a ground connection 816. All nodes A-I connected by a transducer element 802 to either end of the given transducer element 802 to be used for ablation are configured to select a current source 814. The current source 814 connected to the given transducer element 802 to be used for ablation is set to deliver sufficient power to the given transducer element 802 to raise its temperature to 50° C.-100° C., enough to cause non-blood tissue ablation. All of the other connected current sources 814 are adjusted to deliver current so that the voltages at the node A-I they are connected to is a percentage of the voltage at the node A-I connected to the given transducer element 802 being used for ablation. For example, if the transducer element 802e is to be used for ablation, then nodes B, C, D, E, H, and I will be connected to current sources 814b, 814c, 814d, 814e, 814h, 814i, and node A, F, and G will be connected to ground 816. The current source 814e connected to node E will be adjusted so that sufficient power is delivered to transducer element 802e to cause ablation. In doing so, a voltage will be generated at the node E. The current sources 814b, 814d, 814h connected to nodes B, D, and H are set to ensure the voltage at those nodes is, for example 66% of the voltage at node E. The current sources 814c, 8141 connected to nodes C and I are set to ensure the voltages at those nodes is, for example 33% the voltage at node E. In doing do, the power delivered to all transducer elements 802 connected to nodes B, C, D, H, and I will be 11% of the power delivered to the given transducer element 802e, which is insufficient for ablation. It is possible to use different percentages for voltage values than specified herein.
While
There are several ways to improve the accuracy in sensing the voltage drop across the transducer elements to improve accuracy of temperature measurement or flow sensing. One approach to achieve improved accuracy is to use four terminal sensing.
In
In some configurations, being able to minimize the effect of lead resistance when measuring voltage across the transducer elements is possible without adding additional wires.
In temperature sensing or convective cooling sensing mode, leads 610a, 610b (collectively 610) are used to supply and sink the current necessary to cause transducer elements 612a-612e (collectively 612) to produce sufficient heat to be able to measure convective cooling. Leads 614a, 614b are used to measure the voltage across transducer element 612a. Leads 614b, 614c are used to measure the voltage across transducer element 612b. Leads 614c, 614d are used to measure the voltage across transducer element 612c. Leads 614d, 614e are used to measure the voltage across transducer element 612d. Leads 614e, 614f are used to measure the voltage across transducer element 612e. During ablation mode, leads 614a, 614b are used to supply the current to cause transducer element 612a to ablate the non-blood tissue, leads 614b, 614c are used to supply the current to cause the transducer element 612b to ablate, and so on.
As an example, the transducer element 622a between nodes J and O is being used for temperature, flow, or convective cooling sensing. The leads connected to nodes J and O supply the current to the transducer element 622a between the nodes. This causes a measurable voltage drop across the transducer element 622a between nodes J and O. The leads attached to nodes B, D, E, F, I, K, N, P, S, T, U, W are used to sense voltage at the respective nodes. The control system to which the leads are attached is configured so that there is negligible current flow through these leads, and negligible voltage drop across the leads. The leads attached to nodes A, C, G, H, L, M, Q, R, V, and X are actively driven and drive the nodes to a particular voltage. The control system adjusts the voltages at nodes A, C, G, H, and L so that the voltage measured at nodes B, D, E, F, I, and K are all measured to be equal. When this state occurs, the current between nodes E and D, E and B, E and F is negligible and therefore, the current between nodes E and J must be negligible, and node E will be at the same potential as node J. The control system adjusts the voltages at nodes X, R, V, M, and Q so that the voltage measured at nodes W, S, T, U, N, and P are all measured to be equal. When this state occurs, the current between nodes S and T, T and W, T and U is negligible and therefore, the current between nodes T and O must be negligible, and node T will be at the same potential as node O. The voltage drop across the element between nodes J and O is therefore equal to the difference between the voltage at node E and the voltage at node T.
When this circuit 900 is not sensing or ablating, adjustable voltage sources 914a-914h (collectively 914, only eight called out in
In some embodiments, it is beneficial to ensure the entire medical treatment device is electrically insulated from the body. The reasons that this may be desirable are to prevent electrochemical activity from generating offset voltages, prevent leakage currents from affecting measurements and prevent gas bubble generation inside the blood stream.
Sensing Impedance Change
Measuring electrical impedance has been suggested as a way for determining when a catheter probe is in contact with the non-blood tissue of the heart wall. However, distinguishing non-blood tissue from blood using electrical impedance is problematic as the impedance is affected by many factors such as contact pressure and contact area. Also, the transducer element (e.g., electrode) may be in contact with many different materials, each of which has different impedance. However, using permittivity (also known as dielectric constant) measured over a range of frequencies can be used effectively to make the determination between blood and non-blood tissue.
As mentioned, material such as blood, muscle tissue, fat, fibrous material, and calcified tissue each has different impedance. However, in all the materials mentioned, except for blood (and other liquids such as urine) the permittivity drops with increasing frequency. For example, the conductivity of all those materials, including blood, stays nearly constant from DC to over 100 MHz. The permittivity of blood (and most other liquids in the body) is about the same at 1 KHz and 100 Khz, while in all other materials mentioned the dielectric constant drops by about a factor of 4, and typically by at least a factor of 10 between those two frequencies. Therefore, accurate discrimination between blood and non-blood tissue can be made by monitoring the ratio of the permittivity at 1 KHz to the value at 100 KHz. Table 1 and Table 2 show the change of Conductivity and Relative Permittivity with respect to frequency.
A transducer element 1102 carried on a PCB substrate 1104 is in physical contact with a bodily material 1106 (non-blood tissue or blood). The bodily material 1106 is electrically grounded to a same return path 1108 as the circuit 1100. Instead of a return path, a ground electrode adjacent to the transducer element (e.g., electrode) 1102 can be used. An alternate embodiment may be to use a balanced pair of electrodes with equal but opposite phase signals relative to ground. Such a configuration increases immunity to electrical noise. When frequency F1 or F2 is fed to transducer element 1102 from oscillators 1110a, 1110b via a resistor 1112 the phase shift of the signal caused by the dielectric constant of the bodily material 1106 can be measured by a phase meter. The permittivity is the tangent of the phase shift. For better noise immunity both the in-phase component and the out-of-phase, or quadrature, are measured (outputs 1114a, 1114b) then divided to determine the phase shift. The in-phase and out-of phase components are measured by multiplying the voltage signal on transducer element 1102 with the driving signal and with the driving signal phase shifted by 90 degrees using phase shifter 1116 and multipliers 1118. A selector 1119 may be used to selectively switch between coupling the frequencies F1, F2, or no frequency.
A pair of analog-to-digital converters (ADC) 1120 are used to digitize the results, after low pass filtering by capacitor 1122. If desired, the complete operation can be performed digitally by digitizing the signal from the transducer element 1102, since the highest frequency is relatively low. A separate circuit can be used for each transducer element 1102 or a selector 1124 (also known as multiplexer or analog switch) can connect the same circuit to multiple transducer elements 1102 in rapid succession. The time needed for an accurate measurement is typically several milliseconds; therefore even a large grid or array of transducer elements 1102 can be mapped quickly. A same lead 1126 can also be used to feed current for RF ablation using ablation energy source 1128 and a switch 1130. Alternatively a different power source, such as a DC current source, could be connected and provide a voltage and current for directly causing the transducer element 1102 to produce a sufficient amount of heat to cause ablation.
Sensing Force
Another method of distinguishing between non-blood tissue and blood is to measure a force being exerted inwardly on one or more transducer elements mounted or otherwise carried by an expandable frame (e.g., expandable frame 208 of
A force is exerted on a force sensor transducer element 1302 carried by a flexible PCB substrate 1304, by a bodily material 1306, for example blood or non-blood tissue.
A charge amplifier 1308 converts an output of the force sensor transducer element 1302 to a voltage which is digitized by an analog-to-digital (ADC) converter 1310. This voltage is proportional to the force exerted on the force sensor transducer element 1302 by the bodily material 1306, and the output may be indicative of a pressure. An ablation transducer element (e.g., electrode) can be used for temperature monitoring, as explained earlier, or a separate temperature sensor 1312 can be used. A capacitor 1314 can be used to isolate the RF from the DC current used for temperature sensing. Temperature sensing may be used by a temperature controller 1316 to control an ablation power source 1318 to cause an ablation transducer element 1320 to produce an appropriate amount of ablation (e.g., controlling time, temperature, current, power, etc.). A switch 1322 or valve may selectively couple the ablation power source 1318 to the ablation transducer element 1320.
When a polymeric piezoelectric material is used as the force sensor transducer element 1302, it is important to ensure the force sensor transducer element 1302 is sufficiently electrically insulated to eliminate any leakage current. A possible insulating material to use is silicone. Also, integrating an amplifier near the piezoelectric force sensor transducer element 1302 may improve the circuit performance and may make the circuit 1300 less susceptible to leakage current.
Although this circuit 1300 uses multiplexing via connectors 1330a, 1330b to measure the force exerted on the elements, it is also possible to forgo multiplexing and have a circuit dedicated for each element, or a combination of both techniques.
Note that the same piezoelectric sensing grid can also be used in alternate ways to differentiate non-blood tissue from blood. For example, it can be used as an ultrasonic transmitter and receiver to differentiate based on reflection or on damping coefficient.
Frame
The frame provides expansion and contraction capabilities for the component of the medical device (e.g., grid or array of transducer elements) used to distinguish between blood and non-blood tissue. The transducer elements used to sense a parameter or characteristic to distinguish between blood and non-blood tissue may be mounted or otherwise carried on a frame, or may form an integral component of the frame itself. The frame may be flexible enough to slide within a catheter sheath in order to be deployed percutaneously.
The helical members 1402 may be disposed about a shaft 1410. The helical members 1402 may be positioned between opposing stops 1412a, 1412b, which engage the ends of the helical members 1402 to cause expansion. While two helical members are shown, some embodiments may employ a greater or fewer number of helical members 1402.
The frame 1400 is expanded by retracting a shaft 1410. Retracting the shaft 1410 causes the midpoint of the helical members to be forced outward and move toward the interior surface of the cavity in which the frame is positioned.
The helical members 1402 may be constructed of many different types of material including solid wire (such as stainless steel), hollow tube, carbon fiber, or a flexible PCB with a fibreglass or Nitinol backing. The helical members 1402 may form an integral component of the sensing and ablation transducer elements.
The frame 1500 includes a single helical member 1502, a plurality of ribs 1504, and a shaft 1506, oriented approximately parallel to a longitudinal axis of a catheter 1508. The sensor and ablation transducer elements are located along the helical member 1502 and ribs 1504.
There are several variations on the example shown in
The same principles regarding construction and composition of the ribs described for the frame 1400 of
This inflatable member may have one or more passages, collectively 1610, (only three called out in
An advantageous design feature when building an inflatable member that has interior structures, such as blood flow passages 1610 or an inner cavity 1614 is that the walls that form those interior structures should be reinforced to prevent the wall from collapsing or buckling. Such reinforcement can be accomplished in variety of ways. For example, by creating the inner walls using much thicker material, creating ribbed walls with alternating thinner or thicker sections, collectively 1616, (only three called out in
An inflatable frame 1600 as described may be created using a material such as latex. This device may be used as a supporting frame for elements, for example constructed using flexible printed circuit boards.
Joint Assembly
Several of the frames discussed in the preceding section employ joints where transducer elements cross over one another.
The various embodiments described above can be combined to provide further embodiments. All of the U.S. patents, U.S. patent application publications, U.S. patent applications, foreign patents, foreign patent applications and non-patent publications referred to in this specification and/or listed in the Application Data Sheet are incorporated herein by reference, in their entirety. Aspects of the invention can be modified, if necessary, to employ systems, circuits and concepts of the various patents, applications and publications to provide yet further embodiments of the invention.
These and other changes can be made to the invention in light of the above-detailed description. In general, in the following claims, the terms used should not be construed to limit the invention to the specific embodiments disclosed in the specification and the claims, but should be construed to include all medical treatment devices in accordance with the claims. Accordingly, the invention is not limited by the disclosure, but instead its scope is to be determined entirely by the following claims.
This application is a divisional of U.S. patent application Ser. No. 17/500,186, filed Oct. 13, 2021, which is a continuation of U.S. patent application Ser. No. 16/658,820, filed Oct. 21, 2019, now U.S. Pat. No. 11,331,141, issued May 17, 2022, which is a continuation of U.S. patent application Ser. No. 15/784,647, filedOct. 16, 2017, now U.S. Pat. No. 10,828,096, issued Nov. 10, 2020, which is a continuation of U.S. patent application Ser. No. 14/713,190, filed May 15, 2015, now U.S. Pat. No. 9,820,810, issued Nov. 21, 2017, which is a continuation of U.S. patent application Ser. No. 14/564,463, filed Dec. 9, 2014, now U.S. Pat. No. 9,877,779, issued Jan. 30, 2018, which is a continuation of U.S. patent application Ser. No. 13/070,215, filed Mar. 23, 2011, now U.S. Pat. No. 8,932,287, issued Jan. 13, 2015, which is a continuation of U.S. patent application Ser. No. 11/941,819, filed Nov. 16, 2007, now U.S. Pat. No. 8,906,011, issued Dec. 9, 2014, wherein the entire disclosure of each of the applications cited in this sentence is hereby incorporated herein by reference.
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| Number | Date | Country | |
|---|---|---|---|
| 20220142706 A1 | May 2022 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 17500186 | Oct 2021 | US |
| Child | 17584705 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 16658820 | Oct 2019 | US |
| Child | 17500186 | US | |
| Parent | 15784647 | Oct 2017 | US |
| Child | 16658820 | US | |
| Parent | 14713190 | May 2015 | US |
| Child | 15784647 | US | |
| Parent | 14564463 | Dec 2014 | US |
| Child | 14713190 | US | |
| Parent | 13070215 | Mar 2011 | US |
| Child | 14564463 | US | |
| Parent | 11941819 | Nov 2007 | US |
| Child | 13070215 | US |
