WO2003061467A1 - Implantable wireless sensor for pressure measurement within the heart - Google Patents
Implantable wireless sensor for pressure measurement within the heart Download PDFInfo
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- WO2003061467A1 WO2003061467A1 PCT/US2003/002002 US0302002W WO03061467A1 WO 2003061467 A1 WO2003061467 A1 WO 2003061467A1 US 0302002 W US0302002 W US 0302002W WO 03061467 A1 WO03061467 A1 WO 03061467A1
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- sensor
- circuit
- physical property
- inductor
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
- A61B5/0031—Implanted circuitry
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/021—Measuring pressure in heart or blood vessels
- A61B5/0215—Measuring pressure in heart or blood vessels by means inserted into the body
Definitions
- This invention relates to chronically implanted sensors for wirelessly sensing pressure, temperature and other physical properties within the human body. More particularly, the invention concerns a wireless, un-powered micromachined pressure sensor that can be delivered using endovascular techniques to the interior of the human heart.
- the measurement of blood pressure within the human heart provides critical information regarding the organ's function.
- Many methods and techniques have been developed to give physicians the ability to monitor heart function to properly diagnose and treat various diseases and medical conditions.
- a sensor or transducer placed within the chambers of the heart can be used to record variations in blood pressure based on physical changes to a mechanical element within the sensor. This information is then transferred from the sensor to external device that is capable of translating the data from the sensor into a measurable value that can be displayed.
- the drawback of this type of sensor is that there must be a physical connection between the sensor and the external device, thus limiting its use to acute settings.
- One method of manufacturing a sensor capable of measuring pressure is to use a capacitor that is assembled such that the capacitive plates will deform as a result of exposure to externally applied stress. This deformation will result in a change in the capacitance that will be proportional to the applied stress.
- Various patents describe the fabrication and use of capacitor based pressure sensors. The primary limitation of many of these inventions is that the techniques used to fabricate the sensors do not lend themselves to miniaturization necessary for it to be configured as an implantable medical device.
- MEMS devices as described in these patents traditionally use silicon as a substrate for construction of miniature electrical or mechanical structures.
- the resulting sensors are inherently rigid severely limiting the ability to manipulate them into temporarily small packages that would provide the means for non-surgical implantation into the human body.
- a number of patents detail pressure sensors (some capacitive in nature, some manufactured using MEMS based technology) that are specifically designed for implantation into the human body. These sensors suffer from many of the limitations already mentioned with the additional concerns that they require either the addition of a power source to operate the device or the need for a physical connection to a device capable of translating the sensor output into a meaningful display of a physiologic parameter. To overcome these two problems (power and physical connection), the concept of a externally modulated LC circuit has been applied to development of implantable pressure sensors. Of a number of patents that describe a sensor design of this nature, Chubbuck, U.S. Patent No. 6,113,553 is a representative example.
- the Chubbuck patent demonstrates how a combination of a pressure sensitive capacitor placed in series with an inductor coil provides the basis of a wireless, un-powered pressure sensor that is suitable for implantation into the human body. Construction of an LC circuit in which variations of resonant frequency correlate to changes in measured pressure and which these variations can be detected remotely through the use of electromagnetic coupling are further described in Allen et al., U.S. Patent No. 6,111,520, incorporated herein by reference.
- the device embodied by the Chubbuck patent is manufactured using conventional techniques, thus requiring surgical implantation and thus limiting its applicability to areas that are easily accessible to surgery (i.e., skull).
- a biocompatible, wireless, un-powered pressure sensor that for the purposes of introduction and delivery within the human heart can be manipulated into a smaller shape and size by rolling or folding it into a cylindrical form and loaded into a small diameter catheter. Then upon positioning the catheter within the desired chamber of the heart, the sensor can be deployed and through the use super-elastic alloy components in the form of anchors or hooks secured to the interior wall of the heart.
- the present invention describes a sensor that can be fabricated using micro-machining techniques and can be implanted into the human body using non-surgical methods for the measurement of physical parameters.
- This sensor is fabricated using MicroElectroMechanical Systems (MEMS) technology, which allows the creation of a flexible device that is small, accurate, precise, durable, robust, biocompatible, radiopaque and insensitive to changes in body chemistry, biology or external pressure. This device will not require the use of wires to relay pressure information externally nor need an internal power supply to perform its function.
- MEMS MicroElectroMechanical Systems
- the MEMS approach to sensor design lends itself to the fabrication of small, flat sensors that can be formed using biocompatible polymers as substrate materials.
- the pressure sensor described above can then be manipulated into a smaller shape and size by rolling, bending, or folding it into a cylindrical form. This smaller object can then be introduced into the chambers of the human heart using endovascular catheter techniques. Once positioned within the heart, the device unfurls into a preferred flat shape.
- Super-elastic alloy components may be incorporated into the device such as hooks, anchors, harpoons or coils are designed to secure the pressure sensor to the wall of the heart and resist displacement due to movement of the heart wall or from the interaction of blood being pumped through the heart.
- appropriately biocompatible coatings may be applied to the surface of the sensor in order to prevent adhesion of biological substances to the sensor that could interfere with it proper function.
- the pressure sensor can be manufactured using Micro-machining techniques that were developed for the integrated circuit industry.
- An example of this type of sensor features an inductive-capacitive (LC) resonant circuit with a variable capacitor and is described in Allen et al., U.S. Patent No. 6,111,520 incorporated herein by reference.
- LC inductive-capacitive
- the pressure sensor is made of completely passive components having no active circuitry or power sources such as batteries.
- the pressure sensor is completely self-contained having no leads to connect to an external circuit or power source.
- these same manufacturing techniques can be used to add additional sensing capabilities, such as the ability to measure temperature by the addition of a resistor to the basic LC circuit.
- the pressure sensor When introduced into heart, the pressure sensor can provide pressure related data by use of an external measuring device.
- an external measuring device As disclosed in the Allen et al. patent, several different excitation systems can be used.
- the sensor can be electromagnetically coupled to a transmitting antenna. Consequently, a current is induced in the sensors, which oscillates at the resonant frequency of the sensor. This oscillation causes a change in the frequency spectrum of the transmitted signal. From this change, the bandwidth and resonant frequency of the particular sensor may be determined, from which the corresponding change in pressure can be calculated.
- the present invention provides for an impedance system and method of determining the resonant frequency and bandwidth of a resonant circuit within a particular sensor.
- the system includes a transmitting antenna, which is coupled to an impedance analyzer.
- the impedance analyzer applies a constant voltage signal to the transmitting antenna scanning the frequency across a predetermined spectrum.
- the current passing through the transmitting antenna experiences a peak at the resonant frequency of the sensor. The resonant frequency and bandwidth are thus determined from this peak in the current.
- the method of determining the resonant frequency and bandwidth using an impedance approach may include the steps of transmitting an excitation signal using a transmitting antenna and electromagnetically coupling a sensor having a resonant circuit to the transmitting antenna thereby modifying the impedance of the transmitting antenna. Next, the step of measuring the change in impedance of the transmitting antenna is performed, and finally, the resonant frequency and bandwidth of the sensor circuit are determined.
- the present invention provides for a transmit and receive system and method for dete ⁇ nining the resonant frequency and bandwidth of a resonant circuit within a particular sensor.
- an excitation signal of white noise or predetermined multiple frequencies is transmitted from a transmitting antenna, the sensor being electromagnetically coupled to the transmitting antenna.
- a current is induced in the resonant circuit of the sensor as it absorbs energy from the transmitted excitation signal, the current oscillating at the resonant frequency of the resonant circuit.
- a receiving antenna also electromagnetically coupled to the transmitting antenna, receives the excitation signal minus the energy which was absorbed by the sensor.
- the power of the received signal experiences a dip or notch at the resonant frequency of the sensor.
- the resonant frequency and bandwidth are determined from this notch in the power.
- the transmit and receive method of determining the resonant frequency and bandwidth of a sensor circuit includes the steps of transmitting a multiple frequency signal from transmitting antenna, and, electromagnetically coupling a resonant circuit on a sensor to the transmitting antenna thereby inducing a current in the sensor circuit. Next, the step of receiving a modified transmitted signal due to the induction of current in the sensor circuit is performed. Finally, the step of determining the resonant frequency and bandwidth from the received signal is executed.
- Yet another system and method for determining the resonant frequency and bandwidth of a resonant circuit within a particular sensor includes a chirp interrogation system.
- This system provides for a transmitting antenna which is electromagnetically coupled to the resonant circuit of the sensor.
- An excitation signal of white noise or predetermined multiple frequencies is applied to the transmitting antenna for a predetermined period of time, thereby inducing a current in the resonant circuit of the sensor at the resonant frequency.
- the system listens for a return signal which radiates from the sensor.
- the resonant frequency and bandwidth of the resonant circuit are determined from the return signal.
- the chirp interrogation method for determining the resonant frequency and bandwidth of a resonant circuit within a particular sensor includes the steps of transmitting a multi- frequency signal pulse from a transmitting antenna, electromagnetically coupling a resonant circuit on a sensor to the transmitting antenna thereby inducing a current in the sensor circuit, listening for and receiving a return signal radiated from the sensor circuit, and determining the resonant frequency and bandwidth from the return signal.
- the present invention provides an analog system and method for determining the resonant frequency of a resonant circuit within a particular sensor.
- the analog system comprises a transmitting antenna coupled as part of a tank circuit which in turn is coupled to an oscillator.
- a signal is generated which oscillates at a frequency determined by the electrical characteristics of the tank circuit.
- the frequency of this signal is further modified by the electromagnetic coupling of the resonant circuit of a sensor.
- This signal is applied to a frequency discriminator which in turn provides a signal from which the resonant frequency of the sensor circuit is determined.
- the analog method for determining the resonant frequency and bandwidth of a resonant circuit within a particular sensor includes the steps of generating a transmission signal using a tank circuit which includes a transmitting antenna, modifying the frequency of the transmission signal by electromagnetically coupling the resonant circuit of a sensor to the transmitting antenna, and converting the modified transmission signal into a standard signal for further application.
- this patent discloses a simple method of monitoring the pressure within the human heart by inserting a pressure transducer using a catheter and using a small, hand-held read device to measure the pressure easily, safely, inexpensively and accurately. It also includes a method of introducing the sensor into the body by using the steps of folding or rolling the sensor into a cylinder, loading it into a catheter and deploying into the heart by allowing it to unroll or unfold, either by itself or facilitated by the incorporation of a super- elastic alloy component. The same super-elastic element also provides the means to permanently securing the device to the interior of the heart.
- Delivery of the device of the invention to a heart chamber may be accomplished as follows: Using the standard Seldinger technique, the physician gains access to the patient's jugular artery and places a vessel introducer with a hemostatic valve. Under direct fluoroscopic visualization, a flexible guidewire is inserted through the introducer catheter and maneuvered such that its tip is stationed within a chamber of the heart.
- a catheter has a "daisy shape" sensor folded into its distal end, so that the middle, flat section of the sensor is essentially normal to the longitudinal axis of the catheter.
- a solid or hollow cylindrical rod or member is pushed distally to push the sensor from the distal end of the catheter and, optionally, to attach to an inner wall of the heart chamber with an anchor member.
- a coaxial delivery catheter consisting of two hollow extruded polymeric catheters, the smaller of the two disposed inside the larger one, is inserted over the guidewire and through the introducer and advanced distally until its tip is within the heart chamber.
- the smaller catheter has an annular space to hold a folded sensor, which is released when the outer catheter is withdrawn proximally.
- a sensor is attached to a small diameter, proximally extending "safety" or tether wire.
- the sensor and safety wire are also positioned in a lumen in a catheter or in the annular space between two coaxial catheters, but the safety wire runs the entire length of the delivery catheter and extends proximally past the proximal end of that catheter outside the patient.
- the sensor remains secured to the tether wire after the coaxial delivery catheter is removed from the patient.
- the sensor is detached from the tether wire using any of the methods known in the art, and the wire is removed.
- the senor can be loaded into the annular space between the inner and outer catheters by inserting the sensor into a longitudinal slit cut into the outer catheter and attaching a tab on the sensor's surface into a slot cut into the inner coaxial catheter.
- the sensor will be retracted through the slit and positioned in the annular space between the two tubes.
- the rotation of the inner tube is reversed and the sensor emerges through the slit of the outer catheter.
- the sensor can be packaged and stored in a flat configuration.
- the second advantage is that by cutting the longitudinal slit at an angle that is offset from the main axis of the outer tube, the sensor will be biased into a planar configuration as it is forced through the slit during the deployment process.
- a safety wire system can also be used with this mechanism, although the wire may be external to the outer coaxial tube. As described above, the wire will remain attached to the sensor during the deployment process and will stay within the heart chamber while the delivery catheter is removed. Subsequent to insertion and deployment of the stent-graft, the wire will be detached from the sensor and pulled out of the body.
- the detachment of the wire from the sensor can be accomplished in several ways.
- the wire may be simply glued to the sensor using an adhesive.
- a thin-walled, metal or polymer tube is passed along the length of the wire and positioned at the adhesive joint. While holding this tube steady, the wire is then retracted into the tube. Sufficient traction can be applied to the segment of the wire that remains outside of the body to cause the adhesive to joint to fail and allow removal of the wire.
- Fig. 1 is a front view of an embodiment of the invention
- Fig. 2 is a lateral view of the embodiment of the invention shown in Fig. 1;
- Fig. 3 is a lateral view of an embodiment of the invention of Fig. 1 folded for delivery;
- Fig. 4 is a front view of another embodiment of the invention.
- Fig. 5 is a lateral view of a yet further embodiment of the invention.
- Figs. 6 and 7 are each a lateral view of an embodiment of the invention with an anchoring mechanism
- Fig. 8 is an exploded schematic representation of construction of one embodiment of a sensor
- Fig. 9 is a schematic representation of an embodiment of the invention with distributed capacitance
- Figs. 10 and 11 are each a schematic, partial cross-sectional view of an embodiment of a sensor according to the invention.
- Fig. 12 is a schematic representation of an alternate shape for an embodiment of the invention.
- Fig. 13 is a cross-sectional view of the distal end of a delivery catheter with the embodiment shown in Fig. 12;
- Fig. 14 is a schematic of another sensor according to the invention.
- Fig. 15 is a drawing of a read-out device employed according to the invention.
- Fig. 16 is a block diagram of an electrical circuit useful according to the invention. DETAILED DESCRD?TION OF THE INVENTION
- FIG. 1 One embodiment of a sensor according to the invention is shown in Figures 1, 2, and 3, where a disc-shaped sensor 10 comprises a capacitor disk 12 and a wire spiral 14.
- Figure 2 is a lateral view of sensor 10
- Figure 3 is a lateral view of sensor 10 in a folded configuration for insertion.
- sensor 10 is sufficiently flexible to be folded as shown in Figure 4 is an important aspect of the invention.
- a ring 20 comprised of a shape memory alloy such as nitinol has been attached to, for example, with adhesive, or incorporated into, for example, layered within, a sensor 22.
- Figure 5 is a lateral cross-sectional view of a circular sensor 30 having a ring 32 comprised of a shape memory alloy such as nitinol encompassing the outer edge 34 of sensor 30.
- Ring 32 preferably is attached to outer edge 34 by a suitable physiologically acceptable adhesive 36, such as an appropriate epoxy or cyanoacrylate material.
- a suitable physiologically acceptable adhesive 36 such as an appropriate epoxy or cyanoacrylate material.
- the ring will be radiopaque.
- the size of the circular sensors of the invention will vary according to factors such as the intended application, the delivery system, etc.
- the circular sensors are intended to be from about 0.5 to about 3 cm in diameter, with a thickness of from about 0.05 to about 0.30 in.
- the thickness of the ring i.e., the width of the outside surface 38, will preferably be from about 1.5 to about 3.5 times the thickness of the sensor.
- Figures 6 and 7 each represent a lateral view of a sensor with an anchoring member.
- sensor 40 has a screw/coil 42
- sensor 40 has an anchor 44 with umbrella-like projections 46.
- anchor 42 or 44 When pressure is applied to the flat side 48 of sensor 40, anchor 42 or 44 will penetrate a vessel wall, organ wall, or other substrate to cause sensor 36 to remain in a desired position or location.
- an anchoring mechanism such as is shown in Figures 6 and 7 could be attached to ring 32 in Figure 5.
- the pressure sensor of the invention can be manufactured using Micro-machining techniques that were developed for the integrated circuit industry.
- An example of this type of sensor features an inductive-capacitive (LC) resonant circuit with a variable capacitor, as is described in Allen et al., U.S. Patent No. 6,111,520, all of which is incorporated herein by reference.
- the sensor contains two types of passive electrical components, namely, an inductor and a capacitor.
- the sensor is constructed so that the fluid pressure at the sensor's surface changes the distance between the capacitor's parallel plates and causes a variation of the sensor's capacitance.
- a first layer 242 is fabricated from a sheet of polyimide film (e.g. KAPTON, available from Du Pont) upon which a micro-machined copper pattern 244 is deposited. Pattern 244 preferably consists of a circular conductive segment in the center of the sheet surrounded by a spiral coil.
- a second layer 248 comprises a sheet of flexible adhesive through which hole 250 has been cut in the center. (Optionally there may be more than one such layer 248.)
- a final layer 252 is another sheet of polyimide film with a copper pattern 254 that is a mirror image of pattern 244.
- the first, second, and third layers are aligned such that the holes in the middle adhesive layers are centered between the circular conductive segments in the middle of the two outer polyimide layers 242 and 252.
- a capacitor defined as an electric circuit element used to store charge temporarily, consisting in general of two metallic plates separated and insulated from each other by a dielectric
- the two metal spirals on the polyimide sheets 242 and 252 form an inductor component of a miniature electrical circuit.
- the sensor exhibits the electrical characteristics associated with a standard LC circuit.
- An LC circuit is simply a closed loop with only two elements, a capacitor and an inductor.
- the capacitor in the assembled pressure sensor consists of the two circular conductive segments separated by an air gap. If a pressure force is exerted on these segments it will act to deform the outer polyimide sheet and move the two conductive segments closer together. This will have the effect of reducing the air gap between them which will consequently change the capacitance of the circuit. The result will be a shift in the circuit's resonant frequency that will be in direct proportion to the force applied to the sensor's surface.
- the inductor Because of the presence of the inductor, it is possible to electromagnetically couple to the sensor and induce a current in the circuit. This allows for wireless communication with the sensor and the ability to operate it without the need for an internal source of energy such as a battery.
- the sensor if the sensor is located within the chamber of the heart, it will be possible to determine the pressure within the chamber in a simple, non-invasive procedure by remotely interrogating the sensor, recording the resonant frequency and converting this value to a pressure measurement.
- the readout device generates electromagnetic energy that penetrates through the body's tissues to the sensor's implanted location.
- the sensor's electrical components absorb a fraction of the electromagnetic energy that is generated by the readout device via inductive coupling.
- This coupling induces a current in the sensor's circuit oscillates at the same frequency as the applied electromagnetic energy. Due to the nature of the sensor's electro-mechanical system there exists a frequency of alternating current at which the absorption of energy from the readout device is at a minimum. This frequency is a function of the capacitance of the device. Therefore, if the sensor's capacitance changes, so will the frequency at which it minimally absorbs energy from the readout device. Since the sensor's capacitance is mechanically linked to the fluid pressure at the sensor's surface, a measurement of this frequency by the readout device gives a relative measurement of the fluid pressure. If calibration of the device is performed, then an absolute measurement of pressure can be made. See, for example, the extensive discussion in the Allen et al. patent, again incorporated herein by reference, as well as Gershenfeld et al., U.S. Patent No. 6,025,725, incorporated herein by reference.
- the pressure sensor is made of completely passive components having no active circuitry or power sources such as batteries.
- the pressure sensor is completely self-contained having no leads to comiect to an external circuit or power source.
- these same manufacturing techniques can be used to add additional sensing capabilities, such as the ability to measure temperature by the addition of a resistor to the basic LC circuit.
- the capacitor element consists of two plates that are separated by a suitable dielectric material, such as air, inert gas, fluid or a vacuum.
- a suitable dielectric material such as air, inert gas, fluid or a vacuum.
- various coatings could be applied to the surface or between the polymeric layers used to form the sensor. These coating can be used to provide a hermetic seal that will prevent leakage of body fluids into the cavity or permeation of the cavity material (gas, vacuum or fluid) out of the sensor.
- a sensor 270 has a multitude of capacitors 275 formed either as separate elements or as an array. In such a distributed capacitance configuration, there can be a more accurate and more sensitive measurement of pressure.
- the frequency response to the sensor will be in the range of from about 1 to about 200 MH Z , preferably from about 1 to about 100 MH Z , and more preferably from about 2 to about 90 MH Z , with a Q factor of from about 5 to about 150, optionally from about 5 to about 80, preferably from about 40 to about 100, more preferably from about 50 to 90.
- the device is constructed using multiple layers upon lie the necessary circuit elements. Disposed on the top and bottom layer are metal patterns constructed using micro- machining techniques which define a top and bottom conductor and a spiral inductor coil. To provide for an electrical contact between the top and bottom layers small vias or holes are cut through the middle layers. When the layers are assembled, a metal paste is forced into the small vias to create direct electrical connections or conduits.
- a vialess operational LC circuit can be created. This absence of via holes represents a significant improvement to the sensor in that it simplifies the manufacturing process and, more importantly, significantly increases the durability of the sensor making it more appropriate for use inside the human body.
- Figure 10 is a partial cross-sectional review of the sensor shown in Figure 8, where first layer 242, second layer 248, and third layer 252 are sandwiched together.
- a cylindrical space 256 comprises a pressure sensitive capacitor. No via holes are present.
- the sensor 278 shown in Figure 11 comprises a first polyimide layer 280, a second, adhesive layer 282, and a third, polyimide layer 284.
- First layer 280 has a copper pattern comprising a coil 286 and a disk 288, and third layer 284 comprises a coil 290 and a disk 292.
- a cylindrical space 296 comprises a pressure sensitive capacitor.
- a diode 294 connected between coils 286 and 290 creates a non-linear sensor, i.e., a sensor where the frequency change is non-linear as compared to a change in pressure.
- the design of the sensor is not limited to a specific geometric configuration.
- the inductor component is described as a spiral coil.
- Other embodiments of the sensor could utilize oval, rectangular or an amorphous shape.
- Specific electrical, mechanical and biologic advantages could be obtained by employing these various geometric designs.
- a rectangular shaped sensor in which the ratio of length to width was greater than four would greater lend itself to catheter based delivery as is would minimize the radius of curvature required to position the folded device within a small diameter catheter.
- a more elaborate shape, such as one resembling the petals of a flower would lend itself to more complex folding patterns that could facilitate delivery to specific areas of a chamber of the heart.
- a foldable sensor is delivered to the chamber of a patient's heart in the distal end of a delivery catheter.
- the sensor can be regularly or irregularly shaped so that outer portions of the sensor can fold to about a 90° angle as compared to a relatively flat, middle portion of the sensor.
- a daisy or flower-shaped sensor 308 has a capacitor surface 310 connected to a wire 312 that partly follows the outer configuration of sensor 308.
- Petals 314 fold so that sensor 308 with a distal anchor 316 can be "loaded” into a catheter 318, as shown in Figure 13.
- a pushing rod member 322 is pushed distally to cause sensor 308 to be released from catheter 318 and attach to the inner surface of the wall of a heart chamber (not shown).
- rod member 322 will be temporarily affixed to sensor 308 for at least two purposes.
- rod member 322 functions as a safety or tether wire.
- rod member 322 will be capable of twisting or otherwise maneuvering sensor 308 so that anchor 368 will attach to the heart chamber wall. Once sensor 308 is attached, rod member 322 is disengaged from sensor 308 and withdrawn proximally.
- FIG 14 Another, embodiment of a sensor is shown in Figure 14, where circular sensor 330 comprises flexible cut-outs 332.
- the first outer layer 334 comprises a polymide substrate with a copper pattern comprising a coil 340 and several, from 2 to 6, disks 342 to form pressure sensitive capacitors.
- Sensor 330 also comprises at least one adhesive layer (not shown) and a third outer layer corresponding to the first outer layer (not shown).
- sensor 330 has at least one diode connecting the copper coils of the first and third layers.
- the flexible cut-outs 352 facilitate, among other things, folding of sections of sensor 370 for placement in, or arrangement upon, a delivery catheter, such as in Figure 13.
- the sections can also be folded to create either a "Z" shape or, for example, a "U” shape, for other applications. These shapes also allow the central cavity region to remain flat during delivery so than there is no change to the pressure sensitivity of the device. It is within the scope of the invention that variously numbered and shaped cut-outs could be used for particular applications.
- the invention is not limited to the implantation of a single sensor. Since the biological environment within a patient's heart is not necessarily homogeneous, multiple pressure sensors may be introduced into a patient's heart, each being positioned at different locations. In this situation, each sensor may be designed with a unique signature (obtained by changing the resonant frequency of the sensor), so that the pressure measurement derived from one sensor can be localized to its specific position within the heart.
- Q Quality factor
- the transmitted energy will decay exponentially as it travels away from the sensor, the lower the energy available to be transmitted, the faster it will decay below a signal strength that can be detected by the receiving antenna and the closer the sensor needs to be situated relative to the receiving electronics. In general then, the lower the Q, the greater the energy loss and the shorter the distance between sensor and receiving antenna.
- the Q of the sensor will be dependent on multiple factors such as the shape, size, diameter, number of turns, spacing between turns and cross-sectional area of the inductor component.
- Q will be greatly affected by the materials used to construct the sensors. Specifically, materials with low loss tangents will provide the sensor with higher Q factors.
- the implantable sensor accending to the invention is preferably constructed of various polymers that provide the required flexibility, biocompatibility and processing capabilities.
- the materials used are flexible, biocompatible, and result in a high Q factor.
- KAPTON a polyimide
- suitable materials include polyimides, polyesters (e.g., polyethylene terephthalate), liquid crystal polymers (LCP), and polytetrafluoroethylene (PTFE) and co-polymers thereof.
- liquid crystal polymers examples include, but are not limited to, wholly aromatic polyesters such as polybenzoate-naphthalate; polybenzoate-terephthalate; bisphenol-isophthalate; poly- benzoate-terephthalate-ethylene glycol; and polynaphthalate-amino terephthate.
- dielectrics that is, they are poor conductors of electricity (have a low dielectric constant), but are efficient supporters of elecfrostatic fields.
- An important property of dielectric materials is their ability to support an electrostatic field while dissipating minimal energy. The lower the dielectric loss (the proportion of energy lost), the more effective the dielectric material. For a lossy dielectric material, the loss is described by the property termed "loss tangent.” A large loss tangent reflects a high degree of dielectric absorption.
- the middle layer can comprise an adhesive.
- adhesives include flexible, biocompatible materials such as an epoxy or acrylic adhesive.
- LCPs and PTFE have the lowest loss tangents, and construction of pressures sensors from these materials produces the highest Q factor.
- an LC circuit pressure sensor similar to the embodiment shown in Fig. 8 was assembled using successive layers of the following materials: polyimide/copper, acrylic adhesive, polyimide, acrylic adhesive, and copper/polyamide. When electrically characterized, the Q of this sensor was approximately 30.
- a second sensor of the exact same geometry was then fabricated using the following alternate construction: LCP/copper, PTFE/epoxy adhesive (speedboard), and copper/LCP. When tested, this sensor demonstrated a Q factor of 48.
- a thin (i.e., 200 micron) coating of silicone was applied to the LCP sensor detailed above.
- This coating provided sufficient insulation to maintain the Q at 40 in a conductive medium. Equally important, despite the presence of the silicone, adequate sensitivity to pressure changes was maintained and the sensor retained sufficient flexibility to be folded for endovascular delivery.
- One additional benefit of the silicone encapsulation material is that it can be loaded with a low percentage (i.e., 10 - 20%) of radio-opaque material (e.g., barium sulfate) to provide visibility when examined using fluoroscopic x-ray equipment. This added barium sulphate will not affect the mechanical and electrical properties of the silicone.
- the Q factor of a sensor can be increased by suitable selection of sensor materials or a coating, or both. Preferably both are used, because the resulting high Q factor of a sensor prepared in this fashion is especially suitable for the applications described.
- the pressure sensor can provide pressure related data by use of an external measuring device. As disclosed in the Allen et al. patent, several different excitation systems can be used.
- the readout device generates electromagnetic energy that can penetrate through the body's tissues to the sensor's implanted location.
- the sensor's electrical components can absorb a fraction of the electromagnetic energy that is generated by the readout device via inductive coupling.
- This coupling will induce a current in the sensor's circuit that will oscillate at the same frequency as the applied electromagnetic energy. Due to the nature of the sensor's electro-mechanical system there will exist a frequency of alternating current at which the absorption of energy from the readout device is at a minimum. This frequency is a function of the capacitance of the device. Therefore, if the sensor's capacitance changes so will the frequency at which it minimally absorbs energy from the readout device. Since the sensor's capacitance is mechanically linked to the fluid pressure at the sensor's surface, a measurement of this frequency by the readout device can give a relative measurement of the fluid pressure. If calibration of the device is performed then an absolute measurement of pressure can be made
- the circuitry used to measure and display pressure is contained within a simple to operate, battery powered, hand-held electronic unit 400, as shown in Figure 15.
- This unit 400 also contains the antenna needed to perform the electromagnetic coupling to the sensor.
- the antenna may be integrated into the housing for the electronics or it may be detachable from the unit so that it can be positioned on the surface of the body 402 in proximity to the implanted sensor and easily moved to optimize the coupling between antenna and sensor.
- the antenna itself may consist of a simple standard coil configuration or my incorporate ferrous elements to maximize the coupling efficiency.
- the electronic device would feature an LCD or LED display 404 designed to clearly display the recorded pressure in physiologically relevant units such as mm HG.
- the display may be created by integrating a commercially available hand-held computing device such as a Palm® or micro-PC into the electronic circuitry and using this device's display unit as the visual interface between the equipment and its operator.
- a commercially available hand-held computing device such as a Palm® or micro-PC
- the hand-held computer could be detached from the read-out unit and linked to a standard desktop computer. The information from the device could thus be downloaded into any of several commercially available data acquisition software programs for more detailed analysis or for electronic transfer via hard media or the internet to a remote location.
- the present invention provides for an impedance system and method of determining the resonant frequency and bandwidth of a resonant circuit within a particular sensor.
- the system includes a transmitting antenna, which is coupled to an impedance analyzer.
- the impedance analyzer applies a constant voltage signal to the transmitting antenna scanning the frequency across a predetermined spectrum.
- the current passing through the transmitting antenna experiences a peak at the resonant frequency of the sensor.
- the resonant frequency and bandwidth are thus determined from this peak in the current.
- the method of determining the resonant frequency and bandwidth using an impedance approach may include the steps of transmitting an excitation signal using a transmitting antenna and electromagnetically coupling a sensor having a resonant circuit to the transmitting antenna thereby modifying the impedance of the transmitting antemia. Next, the step of measuring the change in impedance of the transmitting antenna is performed, and finally, the resonant frequency and bandwidth of the sensor circuit are determined.
- the present invention provides for a transmit and receive system and method for determining the resonant frequency and bandwidth of a resonant circuit within a particular sensor.
- an excitation signal of white noise or predetermined multiple frequencies is transmitted from a fransmitting antenna, the sensor being electromagnetically coupled to the transmitting antenna.
- a current is induced in the resonant circuit of the sensor as it absorbs energy from the transmitted excitation signal, the current oscillating at the resonant frequency of the resonant circuit.
- a receiving antenna also electromagnetically coupled to the transmitting antenna, receives the excitation signal minus the energy which was absorbed by the sensor.
- the power of the received signal experiences a dip or notch at the resonant frequency of the sensor.
- the resonant frequency and bandwidth are determined from this notch in the power.
- the transmit and receive method of determining the resonant frequency and bandwidth of a sensor circuit includes the steps of fransmitting a multiple frequency signal from transmitting antenna, and, electromagnetically coupling a resonant circuit on a sensor to the transmitting antenna thereby inducing a current in the sensor circuit. Next, the step of receiving a modified fransmitted signal due to the induction of current in the sensor circuit is performed. Finally, the step of determining the resonant frequency and bandwidth from the received signal is executed.
- Yet another system and method for determining the resonant frequency and bandwidth of a resonant circuit within a particular sensor includes a chirp interrogation system.
- This system provides for a fransmitting antemia which is electromagnetically coupled to the resonant circuit of the sensor.
- An excitation signal of white noise or predetermined multiple frequencies is applied to the transmitting antenna for a predetermined period of time, thereby inducing a current in the resonant circuit of the sensor at the resonant frequency.
- the system listens for a return signal which radiates from the sensor.
- the resonant frequency and bandwidth of the resonant circuit are determined from the return signal.
- the chirp interrogation method for determining the resonant frequency and bandwidth of a resonant circuit within a particular sensor includes the steps of transmitting a multi- frequency signal pulse from a transmitting antenna, electromagnetically coupling a resonant circuit on a sensor to the transmitting antenna thereby inducing a current in the sensor circuit, listening for and receiving a return signal radiated from the sensor circuit, and determining the resonant frequency and bandwidth from the return signal.
- a representative block diagram of an electrical circuit that can be used to interrogate the sensor and determine the resonant frequency is shown in Figure 16.
- a transmitter and receiver, i.e., a transceiver 422 has an antenna 424 for generating and receiving signals from a sensor 426.
- Transceiver 422 is an electronic or digital connection with a phase detector 430, a microprocessor 432, and a frequency synthesizer 434. Microprocessor 432 is in turn connected to an interface 436 such as a terminal. Power supply 438 regulates and provides electrical power to the system.
- the present invention also provides an analog system and method for determining the resonant frequency of a resonant circuit within a particular sensor.
- the analog system comprises a transmitting antenna coupled as part of a tank circuit which in turn is coupled to an oscillator.
- a signal is generated which oscillates at a frequency determined by the electrical characteristics of the tank circuit.
- the frequency of this signal is further modified by the electromagnetic coupling of the resonant circuit of a sensor.
- This signal is applied to a frequency discriminator which in turn provides a signal from which the resonant frequency of the sensor circuit is determined.
- the analog method for determining the resonant frequency and bandwidth of a resonant circuit within a particular sensor includes the steps of generating a transmission signal using a tank circuit which includes a transmitting antenna, modifying the frequency of the transmission signal by electromagnetically coupling the resonant circuit of a sensor to the fransmitting antenna, and converting the modified transmission signal into a standard signal for further application.
- the invention further includes an alternative method of measuring pressure in which a non-linear element such as a diode or polyvinylidenedifloride piezo-electric polymer is added to the LC circuit.
- a non-linear element such as a diode or polyvinylidenedifloride piezo-electric polymer
- a diode with a low tum-on voltage such as a Schottky diode can be fabricated using micro-machining techniques.
- the presence of this non-linear element in various configurations within the LC circuit can be used to modulate the incoming signal from the receiving device and produce different harmonics of the original signal.
- the readout circuitry can be tuned to receive the particular harmonic frequency that is produced and use this signal to reconsfruct the fundamental frequency of the sensor.
- the advantage of this approach is two-fold; the incoming signal can be transmitted continuously and since the return signal will be at different signals, the return signal can also be received continuously.
- One additional concern regarding devices designated for long term implantation in the human body is maintenance of electrical stability over time as the environment the sensor has been placed in changes. Under this scenario the sensor's accuracy may drift from its original baseline. It would thus be desirable to have available to the user of the device, a method for determining if the sensor is functioning properly and also to be able to recalibrate the device anytime after it has been implanted.
- This invention therefore also includes a method of using acoustic energy to challenge the sensor and determining to what degree (if any) sensor performance has been degraded. In this method, energy in the ultrasound range is directed towards the sensor and a measurement is made of the mechanical resonance of the sensor membrane. This same measurement can be made at point after the sensor has been implanted.
- a determination of the degree of change in mechanical resonance frequency can be established. This value can then be used to create a calibration factor that can be applied to the pressure reading taken post- implantation in order to adjust the measured value to reflect the actual pressure within the heart chamber.
Abstract
Description
Claims
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US10/054,672 | 2002-01-22 | ||
US10/054,672 US6855115B2 (en) | 2002-01-22 | 2002-01-22 | Implantable wireless sensor for pressure measurement within the heart |
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Also Published As
Publication number | Publication date |
---|---|
US20030139677A1 (en) | 2003-07-24 |
US7481771B2 (en) | 2009-01-27 |
US20050015014A1 (en) | 2005-01-20 |
US6855115B2 (en) | 2005-02-15 |
WO2003061467A8 (en) | 2003-10-23 |
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