WO2001037726A1 - Implant medical interroge a distance equipe d'un detecteur - Google Patents

Implant medical interroge a distance equipe d'un detecteur Download PDF

Info

Publication number
WO2001037726A1
WO2001037726A1 PCT/US2000/032196 US0032196W WO0137726A1 WO 2001037726 A1 WO2001037726 A1 WO 2001037726A1 US 0032196 W US0032196 W US 0032196W WO 0137726 A1 WO0137726 A1 WO 0137726A1
Authority
WO
WIPO (PCT)
Prior art keywords
carrier
medical implant
implant device
annulus
sensor
Prior art date
Application number
PCT/US2000/032196
Other languages
English (en)
Inventor
Eric Weissman
Elmer D. Dickens, Jr.
Original Assignee
Noveon Ip Holding Corp.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Noveon Ip Holding Corp. filed Critical Noveon Ip Holding Corp.
Priority to AU17956/01A priority Critical patent/AU1795601A/en
Publication of WO2001037726A1 publication Critical patent/WO2001037726A1/fr

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6867—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive specially adapted to be attached or implanted in a specific body part
    • A61B5/6876—Blood vessel
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/6862—Stents
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/028—Microscale sensors, e.g. electromechanical sensors [MEMS]
    • 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
    • A61B5/026—Measuring blood flow

Definitions

  • the present invention relates generally to medical implant devices, and more particularly to devices which may be interrogated remotely from outside the body.
  • Implant devices such as pacemakers, artificial joints, valves, grafts, stents, etc. provide a patient with the opportunity to lead a normal life even in the face of major heart, reconstructive, or other type surgery, for example. It has been found, however, that the introduction of such implant devices can sometimes lead to complications. For example, the human body may reject the implant device which can ultimately lead to infection or other types of complications. Alternatively, the implant device may malfunction or become inoperative. Therefore, it is desirable to be able to monitor the condition of the implant device. On the other hand, it is highly undesirable to have to perform invasive surgery in order to evaluate the condition of the device.
  • Techniques which enable the function of an implant device to be monitored remotely from outside the body of the patient. These techniques involve including one or more sensors in the device for sensing the condition of the device.
  • the device further includes a small transceiver for processing the output of the sensors and transmitting a signal based on the output.
  • signal typically is a radio frequency signal which is received by a receiver from outside the body of the patient. The receiver then processes the signal in order to monitor the function of the device.
  • a medical implant device includes a structure implantable within a body of a living animal for assisting in carrying out a function within the body.
  • the device includes a transducer element mounted on a carrier for sensing a parameter associated with the structure.
  • the device includes a communication circuit coupled to the transducer element for producing an output based on the sensed parameter and which serves to communicate the output non-invasively to a receiver located outside the body.
  • the carrier is bonded to the structure such that portion of the structure located immediately beneath the carrier is isolated from stresses generated in regions of the structure not under the carrier.
  • an implantable annulus sensor which includes a base portion and a transducer element mounted on the base portion for measuring a parameter associated with a function occurring within a body of a living animal. Additionally, the sensor includes at least one flexible strap attached to the base portion and which may be wrapped for securing the base portion to a structure within the body of the living animal.
  • a medical implant device which includes a structure implantable within a body of a living animal for assisting in carrying out a function within the body.
  • the device includes a transducer element mounted on a carrier for sensing a parameter associated with the structure, and a communication circuit coupled to the transducer element for producing an output based on the sensed parameter and serving to communicate the output non-invasively to a receiver located outside the body.
  • the device includes a cap for protecting the transducer element from undesired contact with surrounding portions of the body of the living animal.
  • FIG. 1 is a side view of a graft having a remotely interrogatable annulus sensor and patch sensor in accordance with an exemplary embodiment of the present invention
  • Fig. 2 is a cross section of the annulus sensor in accordance with the present invention
  • Fig. 3 is partial view of the annulus sensor showing a preferred flat portion with an array of strain gages in accordance with the present invention
  • Fig. 4 is a partial view of the annulus sensor of Fig. 1 bonded to the graft using an adhesive in accordance with the present invention
  • Fig. 5 is a partial cross section of the annulus sensor of Fig. 1 in an embodiment where the annulus is crimped to the graft in accordance with the present invention
  • Fig. 5A is a partial cross section in which the annulus is crimped to the graft according to another embodiment of the present invention.
  • Fig. 6 is a partial cross section of the annulus sensor of Fig. 1 in an embodiment where the annulus is sewn to the graft in accordance with the present invention;
  • Fig. 7 is a cross section of the annulus sensor in an embodiment which utilizes shape memory alloy fibers to adhere the annulus to the graft;
  • Figs. 8A, 8B and 8C are partial cross sections of the annulus sensor of Fig. 7 illustrating the manner in which the shape memory alloy fibers engage the graft;
  • Fig. 9 is a partial cross section of the annulus sensor in an embodiment using a carrier plate with shape memory alloy fibers to adhere the annulus to the graft;
  • Fig. 1 0 is a side view of an annulus sensor designed to self lock around the graft in accordance with the present invention;
  • Fig. 1 1 is a side view of another embodiment of an annulus sensor designed to self lock around the graft in accordance with the present invention.
  • Fig. 1 2 is a side cross section of an annulus sensor having a protective cap in accordance with the present invention.
  • the system includes a medical implant device which is implanted in a living animal such as a human patient.
  • the medical implant device can be any of a wide variety of different types of devices including, for example, a stent, graft or shunt, artificial joint, etc.
  • Such implant devices typically are configured to carry out or assist in carrying out a function within the patient.
  • the device prevents the closing of an arterial wall and permits the flow of blood therethrough.
  • the device serves to couple blood flow between two separate ends of an artery.
  • the device may instead consist of an artificial hip or knee which facilitates movement of the leg of the patient.
  • Other functions include, but are not limited to, a hemodialysis shunt and spinal brace, for example.
  • the devices include a sensing circuit which serves to sense a parameter associated with the function performed by the device.
  • a sensing circuit which serves to sense a parameter associated with the function performed by the device.
  • the sensor may be used to detect the degree of restenosis which occurs within the device.
  • the sensing circuit may detect an amount of strain or displacement which occurs in an artificial hip or knee.
  • the sensor may serve to sense the condition of the implant device in carrying out its intended function.
  • the sensor may detect the pulse rate.
  • Such known systems further include interrogation instrumentation for remotely interrogating the implant device in order to evaluate the device function.
  • the interrogation instrumentation includes, for example, an interrogator unit which is positioned outside the patient in close proximity to the implant device. The interrogator unit serves to activate the sensing circuit within the implant device and receive information from the device.
  • the sensing circuit includes, for example, a small radio frequency transmitter which transmits the information from the sensing circuit.
  • the sensing circuit may be designed to have a variable impedance loading effect on the interrogator unit.
  • the output of the sensing circuit may vary in relation to the sensed parameter (e.g., blood flow, pressure, amount of restenosis, etc.).
  • Figs. 1 thru 3 the present invention will be described in the context of a medical implant device in the form of a graft or shunt. It will be appreciated, however, that the invention has application in a variety of different types of implant devices such as stents, artificial joints, intramedullary rods, protective plates, etc. Thus, the present invention in its most general sense is not intended to be limited to a particular type of implant device. Nevertheless, it will be appreciated that the present invention is particularly well suited for implants such as grafts, stents, etc.
  • Figs. 1 thru 3 illustrate an embodiment of the invention in which the implant device is a graft 20 for joining separate ends of a blood vessel (not shown).
  • the graft 20 has a tube shaped structure 22 made up of a thin material such as stainless steel, or a composite and/or plastic material. Using known techniques, the graft 20 is implanted within the patient by securing respective ends of a blood vessel to corresponding ends of the graft 20. Consequently, blood will flow through the interior of the graft 20 as represented by arrow 24.
  • the graft 20 further includes an annulus 26 which is fitted around the outer circumference of the tube 1 02.
  • the annulus 26 serves as a carrier for one or more transducer sensing elements 28 (e.g., strain gage elements) which are mounted in or on the outer surface of a flat portion 30 preferably included in the annulus 26.
  • the elements may be distributed about the outer circumference of the annulus 26.
  • the strain gage elements 28 may be mounted on the inner surface of the annulus
  • the annulus 26 with the strain gage elements 28 is designed to sense changes in pressure within the graft 20. As the diameter of the tube 22 expands or contracts radially, such changes are detected by the strain gage elements 28 on the annulus 26. An output produced by the strain gage elements 28 varies in impedance as a function of the change in pressure, and the output is coupled to a sensing circuit 32 via electrical lines 34. Consequently, a change in pressure within the graft 20 results in a variation in the impedance presented to the sensing circuit 32. It has been shown that a change in pressure exerted by the blood within a graft or shunt is a reliable indicator of vascular problems. Such problems may include clogging within the graft or shunt, for example, or clogging within the vessel.
  • the sensing circuit 32 is mounted to the structure 22 as shown in Fig. 1 , or to the annulus 26 itself.
  • the sensing circuit 32 may be based on any of a variety of known techniques suitable for permitting non-invasive interrogation.
  • the sensing circuit 32 may be configured to be interrogated non-invasively using a variable impedance loading effect.
  • Such a configuration is described in detail in commonly assigned, copending United States patent application Serial No. 09/275,308 to Spillman, et al., entitled “Remotely Interrogated Diagnostic Implant Device with Electrically Passive Sensor", filed March 24, 1 999, and in corresponding PCT International Published Application WO005621 0 A. The entire disclosure of each of these applications is incorporated herein by reference.
  • the sensing circuit 32 may be configured to utilize RF telemetry techniques, for example, to transmit a signal to an analyzer outside the body of the patient.
  • the load measured by a strain gage elements 28 in the annulus 26 may serve to change the oscillation frequency of an RF oscillator included in the sensing circuit 32.
  • An antenna (not shown) provided within the sensing circuit 32 serves to transmit the RF signal output by the oscillator to the analyzer which in turn determines the measured load based on the frequency of the received signal. Details on the use of RF telemetry to non-invasively obtain information from medical implants can be found, for example, in United States Patent No. 5,807,258, the entire disclosure of which is incorporated herein by reference. As the particular configuration of the sensing circuit 32 to permit non-invasive interrogation is not critical to the present invention, further details thereof have been omitted for sake of brevity.
  • the graft tube 22 is made of a thin, compliant material which tends to deform measurably as a result of changes in blood pressure within the graft 20.
  • the tube 22 is a conventional graft made of a compliant woven fabric.
  • the annulus 26 preferably is made of a thin, flexible material such as a biocompatible plastic or metal or a paralyene coated material of choice.
  • the annulus 26 includes the strain gage elements 28 formed on the outer surface of the annulus 26.
  • the strain gage elements 28 are piezoresistive devices whose resistance changes as a function of mechanical strain of the annulus in the direction of its circumference.
  • the piezoresistive devices are formed using MEMs technology, patterned lithography, etc., either directly on the annulus 26 material, or are subsequently mounted to the annulus 26 via a suitable adhesive, etc.
  • the outputs of the strain gage elements 28 are combined as desired in parallel, series, as a Wheatstone bridge, etc., via conductive lines 36 (Fig. 3) formed on the annulus 26, for example.
  • the conductive lines 36 are coupled to lines 34 to produce a resistance which varies as a function of the pressure exerted on the annulus 26 by the tube 22.
  • the material of which the annulus 26 is made is preferably stiffer than the woven fabric or other compliant material making up the tube 22.
  • the annulus 26 is placed around the circumference of the tube 22 so as to slightly compress the tube 22.
  • any expansion which occurs in the tube 22 due to blood flowing therethrough will result in an expansion of the annulus 26, and hence a change in the output resistance of the strain gage elements 28.
  • the annulus 26 there is approximately a 0.004 inch increase in diameter of the graft 20, for example, when blood is introduced therethrough at a pressure of 1 00 millimeters of mercury.
  • the annulus 26 will be subjected to the majority of the load due to blood pressure.
  • the annulus 26 is mounted to the outer circumference of the tube 22 according to a number of different techniques described below in connection with Figs. 4-1 1 .
  • the annulus 26 is mounted to the tube 22 using a friction or interference fit.
  • this embodiment is less preferred as it has been found that local motions of the graft 20 are transmitted to the material under the annulus 26 and are detected by the strain gage elements 28.
  • a more preferred embodiment is illustrated in Fig. 4.
  • an adhesive 40 is provided along the edges 42 and 44 of the annulus 26.
  • the adhesive 40 serves to bond the edges 42 and 44 of the annulus 26 to the tube 22.
  • the adhesive 40 may be any suitable type of biocompatible adhesive or an adhesive with a biocompatible covering (not shown).
  • Fig. 5 represents another embodiment for adhering the annulus 26 to the tube 22.
  • the annulus 26 is mechanically crimped to the tube 22 along the edges 42 and 44. More specifically, the annulus 26 includes a groove 46 about the inner circumference along each of the edges 42 and 44.
  • the annulus 26 is placed about the tube 22.
  • An axially directed compression force is exerted on the tube 22 to cause nubs 50 of the compliant material making up the tube 22 to form in the grooves 46.
  • the sides of the annulus 26 are then compressed towards each other along the edges 42 and 44 so as to crimp the annulus 26 in secure fixed engagement with the nubs 50.
  • Fig. 5A shows an embodiment in which the nubs 50 are more pronounced. Again, as a result, the tube material located immediately beneath the flat portion 30 is isolated from stresses generated in regions of the tube 22 not under the annulus 26.
  • the annulus 26 includes predrilled holes 52 about its circumference along each of the edges 42 and 44. The edges 42 and 44 are then sutured or sewn to the wall of the tube
  • the tube 22 uses filament(s) 54.
  • the tube 22 also includes predrilled holes 56, depending upon the material used to form the tube 22 and the ease with which the filament 54 may be inserted through the tube 22.
  • the tube material located immediately beneath the flat portion 30 is isolated from stresses generated in regions of the tube 22 not under the annulus 26.
  • the bonding methods of Figs. 4-6 are also advantageous in that they allow for a simplification of the design. Since only the region of the graft 20 directly under the strain gage elements 28 needs to be isolated from the rest of the graft 20, only the flat portion 30 needs to be so bonded around its perimeter. Since the flat portion 30 will be held in place against the graft tube 22 by such bond, the remainder of the annulus 26 may be dispensed with in another embodiment. In such an embodiment, the sensor is reduced to a simple flat patch with the strain gage elements 28 mounted thereto.
  • the shape of the patch can be rectangular similar to the flat portion 30.
  • the shape of the patch may be circular or some other shape, e.g., ovoid.
  • Fig. 1 shows a circular-shaped patch type sensor 58.
  • the patch sensor 58 can be made of the same material as the annulus 26.
  • the patch sensor 58 is adhered to the tube 22 along its perimeter using any of the methods described above, and particularly the adhesive (Fig. 4), crimping (Fig. 5) or suturing (Fig. 6) .
  • Fig. 7 illustrates another embodiment of the annulus 26.
  • shape memory alloy (SMA) fibers are used to adhere the perimeter of the flat portion 30 to the tube 22.
  • the perimeter of the flat portion 30 includes straight SMA fibers 60 which extend generally radially inwardly as shown in Fig. 7.
  • the annulus 26 is slipped over a flaccid tube 22 and positioned at the desired location as represented in Fig. 8A.
  • an auxiliary bladder (not shown) inserted in the graft tube 22, an application of air or water pressure presses the fibers 60 into the wall of the tube 22 as shown in Fig. 8B.
  • the fibers 60 are designed to penetrate the wall of the tube 22 at least partially as the tube 22 is pressed into engagement. In the case of a woven body tube 22 or thin compliant material, the fibers 60 will penetrate the wall without the need for preformed holes in the tube 22. In the event preformed holes are necessary, such holes can be provided prior to engagement with the fibers 60.
  • the fibers 60 which either partially or completely penetrate the will of the tube 22 are subjected to a thermally induced phase change.
  • the SMA fibers 60 are designed using conventional techniques such that with the thermally induced phase change, the fibers 60 transform to a curled shape designed to fixedly hook the flat portion 30 to the tube 22 as shown in Fig. 8C. Again, the tube material located immediately beneath the flat portion 30 is thus isolated from stresses generated in regions of the tube 22 not under the annulus 26.
  • Fig. 9 illustrates a variation of the embodiment shown in Figs. 7 and 8A-8C.
  • the fibers 60 are initially arrayed on a separate, thin, foil carrier 64 instead of being arrayed on the perimeter of the annulus flat portion 30 as in the embodiment of Figs. 7 and 8A-8C.
  • the carrier 64 is placed inside the graft tube 22 at the desired position with the fibers 60 facing the wall of the tube 22. Mechanical or hydraulic pressure applied to the carrier forces the fibers 60 to protrude through the wall.
  • the protruding fibers 60 are configured so as to slip into a set of matching holes preformed in the annulus 26.
  • a thermally induced phase change is then introduced which causes the fibers 60 to hook and bind the assembly together.
  • the carrier 64 would stay in the graft tube 22.
  • the SMA fibers 60 could be designed to retract from the foil carrier 64 and hook into the wall of the tube 22 as part of the phase change. This would allow the carrier 64 to be removed.
  • Figs. 4-9 can be applied to either an annulus sensor or patch type sensor as will be appreciated.
  • a mounting unit may instead be bonded to the tube 22 using the same techniques.
  • the mounting unit (not shown) is designed to receive the sensor which is configured to be fixedly mounted to the mounting unit (e.g., via a snap-fit into a frame) .
  • the present invention contemplates such variations.
  • Figs. 1 0 and 1 1 relate to annulus sensors which provide for fast yet secure attachment to the graft tube 22 or a native blood vessel, for example, using a self-locking technique.
  • Figs. 1 0 and 1 1 each show an annulus in which a curved loop of the annulus is a self-locking two piece strap that closes around a vein, artery or shunt, for example. Attachment is performed, for example, while the blood vessel is under hydrostatic pressure.
  • the annulus 26' includes a flat portion 30 on which the strain gages 28 are located.
  • Strap pieces 70 and 72 are flexible plastic or metal plates with some bending stiffness, with means of gripping the enclosed blood vessel, etc., and itself. The inherent bending stiffness of the strap pieces 70 and 72 assures a secure closed state as they are forced to slide over and grip one another by interlocking teeth 74.
  • the strap pieces 70 and 72 are of thinner stock than the base having the flat portion 30 to provide flexibility.
  • additional sharp, small pins or SMA pins 76 are located along the edge of the flat portion 30 that serve to grip the vessel wall.
  • 1 0 can be as simple as transition points between thicker and thinner parts of the annulus 26', although they could also be true pinned hinges.
  • the entire annulus 26' can be manufactured by injection molding using nylon, for example.
  • the annulus 26' could be made with only a single hinge point 78 in another embodiment, about which all rotation occurs upon closure.
  • Fig. 1 1 illustrates another embodiment similar to the embodiment of Fig. 1 0.
  • one strap piece 70 has a series of teeth 80
  • the other strap piece 74 has a toothed slot or ring 82 into which the strap piece 70 is inserted. Similar to the straps used to bind a collection of wires, the strap piece 70 may be pulled to close the annulus 26" around a vessel and is secured by the toothed slot or ring 82. In an alternate embodiment, the strap piece 70 does not require teeth as the toothed slot or ring 82 has sufficient bite to directly engage the strap piece 70.
  • the strap pieces 70 and 74 may be, but are not required to be, essentially without bending stiffness. Again, the annulus may be formed using injection molding, for example.
  • the annulus is installed when the graft or native vessel is under hydrostatic pressure, i.e., is not flaccid.
  • the open annulus is placed around the pressurized graft or blood vessel and is closed and tightened while observing the output of the strain gage elements 28. Tightening is stopped when the output of the strain gage elements 28 reaches a non-zero constant value, i.e., further incremental tightening produces insignificant changes in readout.
  • Fig. 1 2 illustrates another feature of the invention whereby a protective cap 88 is introduced to protect the transducer element (e.g., strain gage 28) on the flat portion 30. It may be desirable to prevent unwanted contact of the outer surface of the transducer element 28 by muscle, skin or other body tissue. Any normal (i.e., perpendicular) force transmitted to this surface can alter the deflection of the transducer element causing an error in the pressure measurement.
  • a protective cap 88 is introduced to protect the transducer element (e.g., strain gage 28) on the flat portion 30. It may be desirable to prevent unwanted contact of the outer surface of the transducer element 28 by muscle, skin or other body tissue. Any normal (i.e., perpendicular) force transmitted to this surface can alter the deflection of the transducer element causing an error in the pressure measurement.
  • the cap 88 is provided in accordance with the invention.
  • the cap 88 is made of metal or plastic, for example, and is placed over the transducer element(s) 28 and is fixedly secured around the perimeter of the flat portion 30 as shown in Fig. 1 2, for example.
  • the cap 88 prevents unwanted contact of the outer surface of the transducer element by the surrounding muscle, skin, etc.
  • the cap 88 preferably includes one or more small holes, slots, etc. (generally designated as 90) .
  • the cap 88 is formed of a mesh material with multiple holes, slots, etc.
  • the holes or slots 90 serve to avoid creating a captive air volume in region 92 between the outer surface of the transducer elements 28 and the cap 88.
  • the holes or slots 90 create a means for liquid blood or other fluid to reach the outside of the transducer elements 28 in the case where fluidic pressure surrounding the annulus 26 is of interest.
  • the cap 88 is shown herein only in the context of the annulus sensor, it will be appreciated that the cap 88 may be employed with a patch type sensor without departing from the scope of the invention.
  • the exemplary embodiments involve a strain gage element
  • Another embodiment can incorporate a strain gage which produces a capacitance or inductance that changes as a function of strain as will be appreciated.
  • a strain gage which produces a capacitance or inductance that changes as a function of strain.
  • other different types of transducer sensor elements using cantilever beams, MEMs technology, etc. may be used. The present invention is not intended to be limited to any particular type of sensor element in its broadest sense.
  • the transducer sensing element 28 can be any of a variety of known types of sensors which may be used to sense a functional parameter within the living body. Such parameters may include, but are not limited to, vascular parameters such as blood flow rate, blood pressure, oxygen content, cholesterol, restenosis, glucose level, temperature, etc.; hemotology parameters such as blood gases, blood chemistry, hemoglobin content, etc., and skeletal/muscular parameters such as force, strain, displacement, etc.
  • the element 28 itself may be characterized as an impedance based sensor whose resistance, capacitance and/or inductance varies directly with respect to frequency as a function of the sensed parameter, or another type sensor whose output can be converted into a variable impedance.
  • Exemplary sensor types include electrical, piezoelectric, sonic optical, microfluidic, chemical, membrane, thermal, magnetohydrodynamic, an NMR varient, magnetic, magnetostrictive, biological, microelectromechanical sensors (MEMs), etc.
  • the sensing element 28 may be a MEMs device whose impedance varies as a function of the amount or rate of blood flow through a stent or graft.
  • the sensing element 28 may be a surface acoustic wave (SAW) device which can detect blood flow.
  • SAW surface acoustic wave
  • the sensing element 28 may be a piezoelectric device within a stent or graft for detecting blood pressure.

Abstract

L'invention concerne un implant médical comprenant une structure implantable dans le corps d'un être vivant afin d'assister une fonction du corps. Ce dispositif comprend également un élément transducteur monté sur un support pour détecter un paramètre associé à la structure. De plus, le dispositif comprend un circuit de communication couplé à l'élément transducteur pour générer une sortie basée sur le paramètre détecté, et servant à communiquer la sortie de façon non invasive à un récepteur situé à l'extérieur du corps. Le support est relié à la structure de façon que la partie de la structure située immédiatement en dessous du support soit isolée des contraintes générées dans les régions de la structure n'étant pas situées sous le support.
PCT/US2000/032196 1999-11-23 2000-11-22 Implant medical interroge a distance equipe d'un detecteur WO2001037726A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU17956/01A AU1795601A (en) 1999-11-23 2000-11-22 Remotely interrogated medical implant with sensor

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US16710299P 1999-11-23 1999-11-23
US60/167,102 1999-11-23

Publications (1)

Publication Number Publication Date
WO2001037726A1 true WO2001037726A1 (fr) 2001-05-31

Family

ID=22605942

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2000/032196 WO2001037726A1 (fr) 1999-11-23 2000-11-22 Implant medical interroge a distance equipe d'un detecteur

Country Status (2)

Country Link
AU (1) AU1795601A (fr)
WO (1) WO2001037726A1 (fr)

Cited By (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2849367A1 (fr) * 2002-12-31 2004-07-02 Perouse Laboratoires Procede et dispositif de suivi de l'etat d'une endoprothese implantee
EP1535039A2 (fr) * 2002-07-10 2005-06-01 Orthodata Technologies LLC Capteur extensometrique
US7044911B2 (en) 2001-06-29 2006-05-16 Philometron, Inc. Gateway platform for biological monitoring and delivery of therapeutic compounds
WO2007033333A1 (fr) * 2005-09-14 2007-03-22 Orthodata Technologies Llc Systeme de detection de contrainte telemetrique
WO2007067690A2 (fr) * 2005-12-07 2007-06-14 Drexel University Détection de pression sanguine et forme d'onde de pression sanguine
US8437862B2 (en) 2011-03-29 2013-05-07 Medtronic, Inc. Magnetic field detection using magnetohydrodynamic effect
US8467882B2 (en) 2011-03-29 2013-06-18 Medtronic, Inc. Magnetic field detection using magnetohydrodynamic effect
US8690769B2 (en) 2008-04-21 2014-04-08 Philometron, Inc. Metabolic energy monitoring system
US9075910B2 (en) 2010-03-11 2015-07-07 Philometron, Inc. Physiological monitor system for determining medication delivery and outcome
WO2016050972A1 (fr) * 2014-10-03 2016-04-07 Centre National De La Recherche Scientifique Dispositif medical muni de capteurs a impedance variable
WO2017174688A1 (fr) 2016-04-06 2017-10-12 Instent Dispositif medical muni de capteurs
US10912482B2 (en) 2015-10-23 2021-02-09 Sensome SAS Method for determining at least one type and/or condition of cells and system
US20210059526A1 (en) * 2018-01-18 2021-03-04 Oslo Universitetssykehus Hf Medical implant with wireless communication
US11568990B2 (en) 2016-11-21 2023-01-31 Sensome SAS Characterizing and identifying biological structure

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3661146A (en) * 1968-12-31 1972-05-09 Comp Generale Electricite Transducer arrangement for measuring blood flow
WO1989006513A1 (fr) * 1988-01-25 1989-07-27 Baylor College Of Medicine Sonde biologique implantable et extractible
US5487760A (en) * 1994-03-08 1996-01-30 Ats Medical, Inc. Heart valve prosthesis incorporating electronic sensing, monitoring and/or pacing circuitry
US5634462A (en) * 1993-10-15 1997-06-03 Case Western Reserve University Corrugated inter-fascicular nerve cuff method and apparatus
US5807258A (en) 1997-10-14 1998-09-15 Cimochowski; George E. Ultrasonic sensors for monitoring the condition of a vascular graft
WO1999026530A1 (fr) * 1997-11-25 1999-06-03 Cimochowski George E Implant endoluminal a capacite de detection de parametres
WO1999056614A1 (fr) * 1998-05-07 1999-11-11 Bpm Devices, Inc. Systeme comprenant un dispositif implantable, procedes d'utilisation permettant de determiner la pression sanguine et d'autres parametres sanguins chez l'etre vivant
WO2000056210A1 (fr) 1999-03-24 2000-09-28 Noveon Ip Holdings Corp. Dispositif d'implant diagnostique interroge a distance dote d'un detecteur passif electrique

Patent Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3661146A (en) * 1968-12-31 1972-05-09 Comp Generale Electricite Transducer arrangement for measuring blood flow
WO1989006513A1 (fr) * 1988-01-25 1989-07-27 Baylor College Of Medicine Sonde biologique implantable et extractible
US5634462A (en) * 1993-10-15 1997-06-03 Case Western Reserve University Corrugated inter-fascicular nerve cuff method and apparatus
US5487760A (en) * 1994-03-08 1996-01-30 Ats Medical, Inc. Heart valve prosthesis incorporating electronic sensing, monitoring and/or pacing circuitry
US5807258A (en) 1997-10-14 1998-09-15 Cimochowski; George E. Ultrasonic sensors for monitoring the condition of a vascular graft
WO1999026530A1 (fr) * 1997-11-25 1999-06-03 Cimochowski George E Implant endoluminal a capacite de detection de parametres
WO1999056614A1 (fr) * 1998-05-07 1999-11-11 Bpm Devices, Inc. Systeme comprenant un dispositif implantable, procedes d'utilisation permettant de determiner la pression sanguine et d'autres parametres sanguins chez l'etre vivant
WO2000056210A1 (fr) 1999-03-24 2000-09-28 Noveon Ip Holdings Corp. Dispositif d'implant diagnostique interroge a distance dote d'un detecteur passif electrique

Cited By (27)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7044911B2 (en) 2001-06-29 2006-05-16 Philometron, Inc. Gateway platform for biological monitoring and delivery of therapeutic compounds
US8632463B2 (en) 2001-06-29 2014-01-21 Philometron, Inc. Gateway platform for biological monitoring and delivery of therapeutic compounds
US7357037B2 (en) 2002-07-10 2008-04-15 Orthodata Technologies Llc Strain sensing system
EP1535039A2 (fr) * 2002-07-10 2005-06-01 Orthodata Technologies LLC Capteur extensometrique
JP2005532123A (ja) * 2002-07-10 2005-10-27 オルトデータ テクノロジーズ エルエルシー ひずみ検知システム
EP1535039A4 (fr) * 2002-07-10 2006-08-16 Orthodata Technologies Llc Capteur extensometrique
JP4657713B2 (ja) * 2002-07-10 2011-03-23 オルトデータ テクノロジーズ エルエルシー ひずみ検知システム
FR2849367A1 (fr) * 2002-12-31 2004-07-02 Perouse Laboratoires Procede et dispositif de suivi de l'etat d'une endoprothese implantee
KR101006650B1 (ko) 2005-09-14 2011-01-10 오쏘데이터 테크놀로지스 인크 원격측정용 스트레인 센싱 시스템
WO2007033333A1 (fr) * 2005-09-14 2007-03-22 Orthodata Technologies Llc Systeme de detection de contrainte telemetrique
WO2007067690A3 (fr) * 2005-12-07 2008-03-06 Univ Drexel Détection de pression sanguine et forme d'onde de pression sanguine
WO2007067690A2 (fr) * 2005-12-07 2007-06-14 Drexel University Détection de pression sanguine et forme d'onde de pression sanguine
US8690769B2 (en) 2008-04-21 2014-04-08 Philometron, Inc. Metabolic energy monitoring system
US9075910B2 (en) 2010-03-11 2015-07-07 Philometron, Inc. Physiological monitor system for determining medication delivery and outcome
US8467882B2 (en) 2011-03-29 2013-06-18 Medtronic, Inc. Magnetic field detection using magnetohydrodynamic effect
US8437862B2 (en) 2011-03-29 2013-05-07 Medtronic, Inc. Magnetic field detection using magnetohydrodynamic effect
WO2016050972A1 (fr) * 2014-10-03 2016-04-07 Centre National De La Recherche Scientifique Dispositif medical muni de capteurs a impedance variable
FR3026631A1 (fr) * 2014-10-03 2016-04-08 Ecole Polytech Dispositif medical implantable muni de capteurs
JP2017531484A (ja) * 2014-10-03 2017-10-26 セントレ・ナショナル・デ・ラ・レシェルシェ・サイエンティフィーク センサを備える医用デバイス
CN107405071A (zh) * 2014-10-03 2017-11-28 国家科学研究中心 配备有具有可变阻抗的传感器的医疗装置
CN107405071B (zh) * 2014-10-03 2021-04-06 国家科学研究中心 配备有具有可变阻抗的传感器的医疗装置
US11172885B2 (en) 2014-10-03 2021-11-16 Centre National De La Recherche Scientifique Medical device equipped with sensors
US10912482B2 (en) 2015-10-23 2021-02-09 Sensome SAS Method for determining at least one type and/or condition of cells and system
WO2017174688A1 (fr) 2016-04-06 2017-10-12 Instent Dispositif medical muni de capteurs
US11510577B2 (en) 2016-04-06 2022-11-29 Sensome SAS Medical device provided with sensors
US11568990B2 (en) 2016-11-21 2023-01-31 Sensome SAS Characterizing and identifying biological structure
US20210059526A1 (en) * 2018-01-18 2021-03-04 Oslo Universitetssykehus Hf Medical implant with wireless communication

Also Published As

Publication number Publication date
AU1795601A (en) 2001-06-04

Similar Documents

Publication Publication Date Title
CA2667013C (fr) Procede et appareil pour mesurer une pression a l'interieur d'un systeme de fluide
US6092530A (en) Remotely interrogated implant device with sensor for detecting accretion of biological matter
US6206835B1 (en) Remotely interrogated diagnostic implant device with electrically passive sensor
US7147604B1 (en) High Q factor sensor
WO2001037726A1 (fr) Implant medical interroge a distance equipe d'un detecteur
US7615010B1 (en) System for monitoring the physiologic parameters of patients with congestive heart failure
US8512252B2 (en) Delivery method and system for monitoring cardiovascular pressures
CN107252312B (zh) 检测门静脉和/或肝静脉压力的方法和门静脉高压监控系统
EP1136033B1 (fr) Biotélémétrie passive
US20080077016A1 (en) Monitoring system having implantable inductive sensor
AU754027B2 (en) System including an implantable device and methods of use for determining blood pressure and other blood parameters of living being
CA2631057C (fr) Dispositif implantable de mesure telemetrique de la pression arterielle/temperature dans le coeur
US20080281212A1 (en) Transseptal monitoring device
US20090024042A1 (en) Method and system for monitoring ventricular function of a heart
US20080058652A1 (en) Medical Devices
US20090177225A1 (en) Vascular closure device having sensor
EP1162914A1 (fr) Dispositif d'implant diagnostique interroge a distance dote d'un detecteur passif electrique
WO2004014456A2 (fr) Capteur sans fil implantable destine a la mesure de la pression sanguine a l'interieur d'une artere
EP3773238A1 (fr) Procédé et appareil
WO2001012092A1 (fr) Dispositif implante permettant un diagnostic, pouvant etre interroge a distance et dote d'un capteur electriquement passif
US8231538B2 (en) Perivascular pressure sensor and sensing system
WO2002000118A2 (fr) Mesure du gradient de pression pour detection de stenose de shunt
Ohki et al. Wireless pressure sensing of aneurysms
AU2013224644A1 (en) Implantable device for telemetric measurement of blood pressure/temperature within the heart

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AE AG AL AM AT AU AZ BA BB BG BR BY BZ CA CH CN CR CU CZ DE DK DM DZ EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MA MD MG MK MN MW MX MZ NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT TZ UA UG US UZ VN YU ZA ZW

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): GH GM KE LS MW MZ SD SL SZ TZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE TR BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG

121 Ep: the epo has been informed by wipo that ep was designated in this application
DFPE Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101)
REG Reference to national code

Ref country code: DE

Ref legal event code: 8642

122 Ep: pct application non-entry in european phase