WO2000056241A1 - Acoustic-based remotely interrogated diagnostic implant device and system - Google Patents
Acoustic-based remotely interrogated diagnostic implant device and system Download PDFInfo
- Publication number
- WO2000056241A1 WO2000056241A1 PCT/US2000/007637 US0007637W WO0056241A1 WO 2000056241 A1 WO2000056241 A1 WO 2000056241A1 US 0007637 W US0007637 W US 0007637W WO 0056241 A1 WO0056241 A1 WO 0056241A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- acoustic
- implant device
- output
- stent
- living animal
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
-
- 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
- A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
- A61B2560/02—Operational features
- A61B2560/0204—Operational features of power management
- A61B2560/0214—Operational features of power management of power generation or supply
- A61B2560/0219—Operational features of power management of power generation or supply of externally powered implanted units
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0001—Means for transferring electromagnetic energy to implants
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S128/00—Surgery
- Y10S128/903—Radio telemetry
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
- the transceiver included in the implant device typically includes complex electrical circuitry such as mixers, amplifiers, microprocessors, etc for receiving an interrogation signal and for transmitting a response signal based on the output of the sensors
- complex circuitry has a relatively high cost associated therewith
- the complexity of the circuitry increases the likelihood that the device itself may be defective This would then require further invasive surgery and could even result in physical harm to the patient
- power concerns Some type of circuit for providing power to the transceiver is necessary
- the circuit may be a built-in power source such as a battery, or a circuit which derives operating power from an external excitation signal using magnetic or electromagnetic coupling In either case again the complexity of the circuit and/or the need to replace the battery periodically adds to the cost of the device and increases the opportunity for failure or defects
- the present invention is responsive to the aforementioned shortcomings with conventional devices, and is directed towards an implant device which includes a structure implantable within the living animal, and a sensor comprised in the structure and operatively configured to sense a biological parameter associated with the living animal
- the sensor is responsive to acoustic waves provided from outside the living animal to produce an output indicative of the sensed biological parameter, with the structure being configured to transmit the output so that the output may be received from outside the living animal
- a diagnostic system includes a structure implantable within a living animal and operatively configured to carry out or assist in carrying out a function within the living animal
- the structure exhibits a mechanical transfer function which, in response to mechanical excitation, causes the structure to produce an acoustic signal having a characteristic which is modulated in relation to a parameter associated with the carrying out the function
- the system further includes an exciter for acoustically transferring mechanical energy to the structure from outside the living animal, and a receiver located outside the living animal which detects the acoustic signal produced by the structure, processes the acoustic signal in relation to the mechanical transferfunction, and provides an output indicative of the parameter based on the processed acoustic signal
- FIG 1 is an environmental view illustrating a system including a remotely interrogated medical implant device and broadband acoustic analyzer in accordance with the present invention
- Fig 2 is a block diagram of the broadband acoustic analyzer in accordance with the present invention.
- Fig 3 is a partial schematic view representing an acoustic source/detector unit included as part of the acoustic analyzer, the source/detector unit being shown in physical proximity to an implant device being interrogated in accordance with the present invention
- Fig 4 is a block diagram of the source/detector unit in accordance with the present invention
- Fig 5 is a block diagram of the broadband frequency response of the source/detector unit in accordance with the present invention
- Fig 6 is a flowchart illustrating steps for interrogating a stent to estimate restenosis according to one embodiment of the present invention
- Fig 7 is a graph illustrating a variation in damping constant of a stent as a function of degree of restenosis in accordance with the present invention
- Fig 8 is a cross-section view of a dual-cylinder stent in accordance with the present invention
- Fig 9 is a cross-section view taken along line 9-9 of the stent in Fig 8 in accordance with the present invention
- Fig 10 is schematic view representing an acoustic source/detector and the stent of Figs 8 and 9 in accordance with the present invention
- Fig 11 is a graph illustrating a change in resonance decay time as a function of degree of restenosis in accordance with the present invention
- Figs 12a and 12b are cross-section views illustrating a stent with different degrees of restenosis
- Fig 13 is a schematic view of an acoustically powered graft in accordance with another embodiment of the invention.
- Fig 14 is an electrical block diagram of the graft in Fig 13 in accordance with the present invention
- Fig 15 is schematic diagram of acoustically driven power source in accordance with the present invention
- Fig 16 is a schematic diagram of an acoustically driven power source in accordance with another embodiment of the present invention.
- Fig 17 is a block diagram of a transmitter in accordance with one embodiment of the present invention.
- Fig 18 is a block diagram of a transmitter in accordance with another embodiment of the present invention.
- a system for remotely interrogating a medical implant device is generally designated 30
- the system 30 includes a medical implant device 32 which is implanted in a living animal such as a human patient 34
- the medical implant device 32 can be any of a wide variety of different types of devices including for example a stent, graft, artificial joint, etc
- the device 32 preferably is configured to carry out or assist in carrying out a function within the patient 34
- a stent the device 32 prevents the closing of an arterial wall and permits the flow of blood therethrough
- the device 32 serves to couple blood flow between two separate ends of a blood vessel
- the device 32 may instead consist of an artificial hip or knee which facilitates movement of the leg of the patient 34
- Other type devices include, but are not limited to, a hemodialysis
- the device 32 includes a sensor (not shown in Fig 1 ) which serves to sense a parameter associated with the function performed by the device
- a sensor (not shown in Fig 1 ) 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 32
- the sensor 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
- the sensor in such case, requires electrical power in order to operate
- the present invention includes, in part, providing electrical energy to the device 32 by way of acoustic excitation
- the device 32 includes a mechanism for converting acoustic energy provided from outside the body of the patient 34 into electrical energy which is stored for electrically driving the device 32
- the device 32 has a mechanical transferfunction which is responsive to mechanical energy
- the mechanical transfer function varies in a known manner relation to the condition of the implant device 32.
- the system 30 further includes an acoustic analyzer 36 for remotely powering and/or interrogating the implant device 32 in order to evaluate the device function
- the analyzer 36 in the exemplary embodiment includes a broadband acoustic source/detector unit 38 which is positioned outside the patient 34 in close proximity to the implant device 32
- the source/detector unit 38 serves to excite the device 32 with acoustic energy
- the acoustic energy in turn powers the device 32 and/or is used to evaluate the mechanical transfer function of the device 32
- the source/detector unit 38 may then receive acoustic signals radiated by the device 32 in response to the excitation Such signals can then be processed by the analyzer 36 to detect a parameter of interest (e g , blood flow, amount of restenosis, etc )
- a parameter of interest e g , blood flow, amount of restenosis, etc
- the source/detector unit 38 is coupled via an electrical cable 40 to the main circuitry 42 included in the analyzer 36
- the main circuitry 42 includes suitable circuits for driving the source/detector unit 38 as described below, and for processing the output of the source/detector unit 38 in order to provide an output to an operator (e g , display 44)
- the present invention utilizes acoustic coupling between the source/detector unit 38 and the implant device 32
- the device 32 is designed to respond to acoustic energy transmitted by the source/detector 38 in a manner which eliminates the need for complex electronics power supplies, etc within the device In this manner the device 32 can be a very simple, relatively low cost device which is less prone to failure
- the device 32 does not require an active transmitter, mixer, amplifier, etc as in other conventional devices
- the patient 34 is exposed to less high frequency radiation as compared to other types of remotely interrogated implant devices thus improving the safety of the device
- acoustic analyzer 36 in accordance with the exemplary embodiment is illustrated in more detail
- the source/detector unit 38 preferably is a hand-held sized device which is held by a doctor, nurse or medical assistant outside the body of the patient 34 in close proximity to the implant device 32 Since the system 30 is non-invasive the source/detector unit 38 may be placed adjacent
- the analyzer 36 includes a data processing and control circuit 52 which is programmed to carry out the various control and computational functions described herein More particularly, the circuit 52 provides a control signal on control bus 54 The control signal controls the frequency (within the acoustic frequency band) at which the source/detector 38 excites the device 32 by emitting acoustical energy while positioned in close proximity to the device 32 as shown In addition, the control circuit 52 provides a control signal on bus 54 in order to control whether the source/detector 38 is transmitting acoustic energy or receiving acoustic energy reradiated from the device 32 in response to being excited
- the source/detector 38 receives acoustic energy transmitted from the device 32 and converts the energy into an electrical signal on line 56
- the signal on line 56 is input to a signal conditioning circuit 58 which conditions the signal prior to being input to the control circuit 52
- the control circuit 52 processes and analyzes the signal on line 56 in order to determine a parameter associated with the device.
- the excitation signal from the source/detector 38 is used to induce a mechanical resonance in the device 32
- the source/detector 38 detects the response of the device 32 to such mechanical resonance by analyzing, for example, any harmonics which are present as determined by the acoustical energy radiated by the resonating device 32
- the circuit 52 may analyze the decay time associated with the mechanical resonance in response to excitation by the source/detector 38
- the presence of harmonics and/or the decay time can be correlated to the function performed by the implant device
- the presence of harmonics in a stent 32 may increase or decrease as a function of the degree of restenosis which occurs within the stent
- the mechanical resonance decay time of the stent 32 may increase or decrease as a function of the amount of restenosis present in the stent
- the system 30 can analyze changes in the mechanical resonance frequency itself and correlate such changes to the amount of restenosis
- the scope of the present invention is intended to encompass any and all such correlations which may be found between the parameter of interest the acoustic excitation and the response of the device
- Fig 3 provides a perspective view of the source/detector 38 in relation to a stent type device 32 located in a blood vessel 59
- the source/detector 38 includes a two-dimensional (mxn) array 60 of miniature acoustic devices 62
- Each device 62 is made up of an electro-acoustic transducer such as a piezoceramic device In a transmit or excite mode, each device 62 is responsive to an electrical driving signal so as to emit an acoustic wave
- each device is designed to receive an acoustic wave and convert the received wave into an electrical signal The level of the signal is based on the intensity of the received wave
- the preferred embodiment utilizes an array 60 of piezoceramic devices 62, other type devices can also be used without departing from the scope of the invention
- the devices 62 are arranged in a generally planar array
- the active faces of the devices 62 are oriented in a common direction so as to be directed downward towards the implant device 32
- a housing 64 (shown in cut-away) provides a protective enclosure for the source/detector 38, with an acoustic window provided in the housing 64 to allow acoustic waves to be emitted and received by the devices 62
- an electrical input output 66 of each device 62 in the array 60 is hardwired together with the others in parallel
- the input/outputs 66 are selectively connected via a switch 68 to either the output of a voltage controlled oscillator (VCO) 70 or a received signal line 72
- VCO voltage controlled oscillator
- a control signal on line 74 from the control circuit 52 causes the switch 68 to couple the output of the oscillator 70 to the input/output 66 of each of the devices 62
- the control circuit 52 provides a control voltage on line 76 to control the frequency of the VCO 70
- the VCO 70 preferably is an oscillator which is designed to produce an output signal at any frequency within the acoustical range of 50 kilohertz (kHz) to 10 megahertz (MHz) Furthermore, it is desirable that each of the devices 62 provide a generally uniform response throughout the range However, with existing piezoceramic devices 62 currently available, each device has a generally narrow band of operation (e g , on the order of ⁇ 5% about its center operating frequency f op ) Consequently, the array 60 in the present invention is made up of devices 62 selected with different operating frequencies f op uniformly distributed across the broadband acoustical range of 50 kHz to 10 MHz As a result, the composite response of the devices 62 is generally uniform as represented in Fig 5
- the array 60 is able to transmit and detect acoustic energy regardless of the particular frequency at which the device 32 is to be excited or at which the device 32 emits acoustic energy in response to excitation
- the operating frequencies f op of the devices 62 are selected so that at least one device 62 is responsive to the excitation signal from the VCO 70 in order to emit an acoustic signal at each frequency
- at least one device 62 is responsive in the receive mode to detect the respective frequencies reradiated by the device 32, including any harmonics
- the devices 62 with the different operating frequencies f op are spatially distributed within the array 60 Such spatial distribution preferably is selected so that the respective operating frequencies will be uniformly distributed across the array 60 and the overall frequency response of any region within the array 60 will be the same as the other For example regions 80 and 82 each preferably contain a sufficient number of devices 62 with selected operating frequencies to exhibit the same response curve shown in Fig 5 Therefore, it will be appreciated that the overall array 60 will function as a broadband source/detector generally independent of the particular region (e g , 80 or 82) which is positioned immediately adjacent the device 32 The array 60 therefore will be operative throughout the entire acoustic frequency band of interest
- the stent device 32 may be a conventional stent which generally consists of a cylindrical tube
- the tube may be made of metal such as stainless steel, or another material such as plastic and/or a composite material
- the tube wall may be uniform helical or some other geometry
- the stent 32 inherently has physical mass and hence will have a mechanical resonance based upon its physical configuration and the material of which it is made Such mechanical resonance will occur at its resonant frequency ⁇ R (or frequencies in the case of these being multiple mechanical resonances)
- the inventors have recognized that if the stent 32 is excited at its resonant frequency ⁇ R and the excitation is turned off, the stent 32 will reradiate acoustic energy at the resonant frequency ⁇ R and harmonics thereof, i e , 2 ⁇ R , 3 ⁇ R 4 ⁇ R , etc
- the reradiated signal will be damped by a factor of e al
- empirical study and/or modeling it can be determined that the damping coefficient '
- Fig 7 illustrates how the damping coefficient a varies with respect to degree of restenosis
- a level 0 restenosis represents no occlusion in the stent and the damping coefficient a is at a local minimum
- a level 1 restenosis represents complete occlusion at which the damping coefficient a is at a local maximum
- the stent 32 can be said to have a mechanical transfer function which varies in relation to the degree of restenosis
- P 0 and P represent power level at the resonant and first harmonic frequencies, respectively
- Fig 6 is a flowchart representing the above analysis as carried out by the system 30 in accordance with one embodiment of the invention
- the data processing and control circuit 52 includes a microprocessor which is programmed to carry out the appropriate control and processing described herein
- step 100 the system 30 initializes itself by ascertaining the most suitable resonant frequency ⁇ R of the stent 32 More particularly, the source/detector unit 38 is held in close proximity to the patient's body with the array 60 facing the stent 32 (e g , as represented in Fig 1 ) The control circuit 52 (Fig
- the control circuit 52 determines at which frequency in the acoustic frequency band the reradiated acoustic energy is at its highest level as detected by the source/detector 38 Such maximum energy frequency level will correspond to the most suitable resonant frequency ⁇ R of the stent 32, typically, and thus the control circuit 52 ascertains the resonant frequency ⁇ R
- the control circuit 52 causes the source/detector 38 to excite the stent 32 with a brief burst of acoustic energy at the resonant frequency ⁇ R
- the control circuit 52 changes the position of the switch 68 so that the acoustic energy reradiated by the stent 32 in response to the excitation can be detected
- the detected energy is input to the control circuit 52 from the conditioning circuit 58
- the control circuit 52 then
- the control circuit 52 takes the Fourier transform of the time series data in step 106
- the Fourier transform yields among other things, the energy components of the reradiated acoustic energy at the resonant frequency ⁇ R and the first harmonic These values for P 0 and P, respectively, are then used by the control circuit 52 in step 108 to compute the damping coefficient a based on Equ 1 above.
- the control circuit 52 then compares the value of the damping coefficient a with a table stored in memory representing the graph of Fig 7, for example Based on the value of a, the control circuit 52 estimates the degree of restenosis as represented in step 110 The control circuit 52 may then provide an output on the display 44 or the like indicating such estimate Moreover the control circuit 52 may store such information in memory for future use in trending or the like
- the control circuit 52 may use other known data analysis techniques to analyze the frequency content of the acoustic energy reradiated from the stent 32
- wavelet transformations and/or neural network techniques may be employed by the control circuit Moreover, such techniques may be modified to account for different conditions in taking the measurements such as large muscle mass, nearby bone structures, etc Additionally, the control circuit 52 may employ such techniques as pattern recognition to analyze the reradiated acoustic energy
- the control circuit 52 may be programmed to carry out pattern recognition to analyze the class of resonant frequencies exhibited by the stent 32 in response to the acoustic excitation
- Figs 8 and 9 illustrate a specially designed acoustic reradiating stent 120 which can be substituted for the otherwise conventional stent 32 described above
- the stent 120 is made up of two hollow concentric cylinders 122 and 124 which are mechanically connected so that the entire structure has a pronounced mechanical resonance at a resonant frequency ⁇ R within the acoustic frequency band
- the outer cylinder 122 and the inner cylinder 124 are each made of a biocompatible material such as stainless steel, plastic, etc
- the outer cylinder 122 is mechanically connected to the inner cylinder 124 by resilient connecting members 126
- the connecting members 126 are made of a resilient material such as rubber or plastic
- Each member 126 is sufficiently rigid to maintain generally a physical separation between the two cylinders, yet is sufficiently resilient to allow for relative movement between the cylinders 122 and 124 at the resonant frequency ⁇ R
- the connecting members 126 are equally spaced around the circumference of the cylinders
- the stent 120 further includes a seal ring 128 at each end which seals off the circumferential area between the two cylinders 122
- the seal rings 128 prevent blood from entering the area between the cylinders
- the seal rings 128 are made up of a resilient material such as rubber or plastic similar to the connecting members 128
- the stent 120 will exhibit a pronounced mechanical resonance based on the relative motion which can occur between the two concentric cylinders
- the stent 120 may be utilized in accordance with the system 30 as described in relation to Fig 6
- the damping coefficient may be calculated based on the harmonic ratio and used to estimate occlusion as described above
- the degree of restenosis may be estimated using a different, albeit related, criteria
- Fig 10 illustrates represents a configuration of the system 30 in which the decay time of the reradiated acoustic energy is utilized to estimate restenosis More particularly, the stent 120 is excited at its resonant frequency ⁇ R in a manner similar to that described above in steps 100 and 102 in Fig 6 Upon switching the switch 68 from excite mode to receive mode, the array 60 is then used by the control circuit 52 to detect the acoustic energy reradiated from the stent 120 at the resonant frequency ⁇ R In this particular embodiment, the control circuit 52 filters out any harmonics received from the source/detector 38 using a Fourier transform or adjustable filter, for example, and concentrates on the acoustic energy received at the resonant frequency ⁇ R
- control circuit 52 measures the amplitude of the reradiated acoustic energy overtime in order to determine the decay time of the mechanical resonance
- the cross section of the stent 120 will be filled with blood 130 as represented in Fig 12a
- the non-occluded stent 120 will have a characteristic acoustic reradiation frequency and decay time following excitation as represented by curve
- the non-blood tissue 136 will begin to fill the cross section of the stent 120 as shown in Fig 12b Depending on the particular design of the stent 120, the restenosis build-up will modify either the decay time of the reradiated acoustic energy, the resonant frequency ⁇ R , or both
- the stent 120 varies in decay time as a function of increasing restenosis
- the decay time may decrease as restenosis increases as represented by curve 136 in Fig
- the control circuit 52 is programmed to estimate the degree of restenosis Such estimate can De based on expected values stored in the circuit 52 In addition, or in the alternative, the measured decay time can be stored in memory in the circuit 52 for purposes of trending
- Fig 13 illustrates another aspect of the invention whereby the acoustic energy from the source/detector 38 is used to provide operating power to an implant device
- Fig 13 illustrates a graft 150 in accordance with the present invention
- the graft 150 is tube shaped and is surgically inserted between two ends of a blood vessel 59 as is conventional
- the graft 150 serves to permit blood flow between the respective ends of the vessel 59
- the body of the graft 150 may be made of metal, plastic, a composite material, etc
- the graft 150 includes a sensor 152 which is mounted, for example, on an inner wall of the tube as shown in Fig 13
- the sensor 152 may be of a type designed to provide an impedance which varies as a function of the rate of bloodflow through the vessel, the amount of restenosis, the oxygen level within the blood therein, etc
- the sensor 152 is connected by way of wires 154 to a main circuit 156 formed within a sealed housing and mounted to an outer wall of the tube, for example
- the main circuit 156 includes a miniature transmitter 158 and a power supply
- the transmitter 158 is designed to transmit a signal which is encoded with information based on the parameter sensed by the sensor 152 As is described below in connection with Figs 17 and 18, the transmitted signal may be an electromagnetic signal, magnetic signal, or an acoustic signal, for example
- the power supply 160 provides operating power to the transmitter 158 and/or the sensor 152, as needed Fig 15 illustrates in detail the configuration of the power supply 160 in accordance with the exemplary embodiment
- the power supply 160 includes a cylindrical permanent magnet 162 oriented as a core within a miniature coil 164
- the power supply 160 further includes spring members 166 attached between respective ends the core 162 and a support frame 168
- the spring members 166 allow the core 162 to move laterally relative to the axis of the coil 164 in an oscillating manner as represented by arrow 170 Movement of the core 162 relative to the coil 164 induces a current in the coil 164
- Such induced current is output through coil terminals 172 and is input to a diode rectifier circuit 174 included in the power supply 160
- the output terminals of the rectifier circuit 174 are coupled across a capacitor 176 so that the energy of the induced current is stored as charge across the capacitor 176
- the output terminals 178 across the capacitor 176 are coupled to the transmitter 158 to
- Fig 16 illustrates an alternative embodiment of the power supply 160 in this case designated 160'
- the power supply 160' includes a plurality of elements 180 connected in parallel
- Each element 180 includes a core 162 coil 164 and rectifier circuit 174 configuration similar to that shown in Fig 15
- the respective positive and negative outputs of the rectifier circuit 174 in each element 180 are connected in parallel and coupled to the storage capacitor 176 In this manner the currents induced in each coil 164 for each element 180 are summed together to produce a total charge which is stored in the capacitor 176
- the spatial orientation of the coils 164 in each element 180 is different Consequently, when the power supply 160' is excited by an acoustic signal (e g , from source/detector 38) at the resonant frequency, the orientation of the array of elements 180 relative to the excitation signal will minimally affect the power output of the supply 160'
- Figs 17 and 18 illustrate exemplary embodiments of the transmitter 158 in accordance with the invention
- Fig 17 represents an acoustic embodiment in which the transmitter 158 transmits an acoustic signal whose frequency varies based on a sensed parameter
- the transmitter 158 includes an oscillator circuit 180 which produces an output signal having a frequency within the acoustic frequency range and which varies as a function of the impedance presented by the sensor 152
- the transmitter 158 further includes a piezoelectric element 182 which converts the electrical signal output from the oscillator 180 into an acoustic signal which in turn is transmitted through the body of the patient
- the oscillator circuit 180 is designed to produce an output signal in the radio frequency band The frequency of the output signal again is varied based on the output of the sensor
- the output signal is coupled to an antenna 184 which is used to transmit the signal to a receiver located outside the body of the patient Again by analyzing the frequency of the detected signal, the sensed parameter may be ascertained
- the present invention provides a system by which operating power for a medical implant device may be provided simply and externally via acoustic energy While the invention is described in the context of a graft 150 it will be appreciated that a wide variety of other types of implant devices may be substituted instead yet still remain within the intended scope of the invention While a moveable coil/core arrangement is described in connection with the embodiment of Fig. 15, it will be appreciated that other mechanisms are available for converting the acoustic energy provided from outside the body into electrical energy For example, a piezoelectric transducer may be utilized in place of the coil/core arrangement
Abstract
Description
Claims
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2000606150A JP2002538934A (en) | 1999-03-24 | 2000-03-23 | Implantation devices and systems that send signals remotely on an acoustic basis to aid in diagnosis |
AU39111/00A AU3911100A (en) | 1999-03-24 | 2000-03-23 | Acoustic-based remotely interrogated diagnostic implant device and system |
EP00918272A EP1162922A1 (en) | 1999-03-24 | 2000-03-23 | Acoustic-based remotely interrogated diagnostic implant device and system |
CA002364853A CA2364853A1 (en) | 1999-03-24 | 2000-03-23 | Acoustic-based remotely interrogated diagnostic implant device and system |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/275,311 US6170488B1 (en) | 1999-03-24 | 1999-03-24 | Acoustic-based remotely interrogated diagnostic implant device and system |
US09/275,311 | 1999-03-24 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2000056241A1 true WO2000056241A1 (en) | 2000-09-28 |
Family
ID=23051751
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US2000/007637 WO2000056241A1 (en) | 1999-03-24 | 2000-03-23 | Acoustic-based remotely interrogated diagnostic implant device and system |
Country Status (6)
Country | Link |
---|---|
US (1) | US6170488B1 (en) |
EP (1) | EP1162922A1 (en) |
JP (1) | JP2002538934A (en) |
AU (1) | AU3911100A (en) |
CA (1) | CA2364853A1 (en) |
WO (1) | WO2000056241A1 (en) |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8082041B1 (en) | 2007-06-15 | 2011-12-20 | Piezo Energy Technologies, LLC | Bio-implantable ultrasound energy capture and storage assembly including transmitter and receiver cooling |
US8165677B2 (en) | 2004-07-09 | 2012-04-24 | Cardiac Pacemakers, Inc. | Method and apparatus of acoustic communication for implantable medical device |
US8974366B1 (en) | 2012-01-10 | 2015-03-10 | Piezo Energy Technologies, LLC | High power ultrasound wireless transcutaneous energy transfer (US-TET) source |
Families Citing this family (105)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20030036746A1 (en) * | 2001-08-16 | 2003-02-20 | Avi Penner | Devices for intrabody delivery of molecules and systems and methods utilizing same |
US6432050B1 (en) * | 1997-12-30 | 2002-08-13 | Remon Medical Technologies Ltd. | Implantable acoustic bio-sensing system and method |
US6361554B1 (en) * | 1999-06-30 | 2002-03-26 | Pharmasonics, Inc. | Methods and apparatus for the subcutaneous delivery of acoustic vibrations |
US6387116B1 (en) * | 1999-06-30 | 2002-05-14 | Pharmasonics, Inc. | Methods and kits for the inhibition of hyperplasia in vascular fistulas and grafts |
US6802857B1 (en) * | 2000-10-11 | 2004-10-12 | Uab Research Foundation | MRI stent |
US7024248B2 (en) * | 2000-10-16 | 2006-04-04 | Remon Medical Technologies Ltd | Systems and methods for communicating with implantable devices |
US6764446B2 (en) | 2000-10-16 | 2004-07-20 | Remon Medical Technologies Ltd | Implantable pressure sensors and methods for making and using them |
US7198603B2 (en) * | 2003-04-14 | 2007-04-03 | Remon Medical Technologies, Inc. | Apparatus and methods using acoustic telemetry for intrabody communications |
US6628989B1 (en) * | 2000-10-16 | 2003-09-30 | Remon Medical Technologies, Ltd. | Acoustic switch and apparatus and methods for using acoustic switches within a body |
US7283874B2 (en) | 2000-10-16 | 2007-10-16 | Remon Medical Technologies Ltd. | Acoustically powered implantable stimulating device |
US6539947B2 (en) * | 2000-12-12 | 2003-04-01 | International Business Machines Corporation | Apparatus, system, method and computer program product for controlling bio-enhancement implants |
US20030060695A1 (en) * | 2001-03-07 | 2003-03-27 | Connelly Patrick R. | Implantable artificial organ devices |
US20040225326A1 (en) * | 2001-05-07 | 2004-11-11 | Weiner Mike L. | Apparatus for the detection of restenosis |
US7160258B2 (en) | 2001-06-26 | 2007-01-09 | Entrack, Inc. | Capsule and method for treating or diagnosing the intestinal tract |
US7727221B2 (en) * | 2001-06-27 | 2010-06-01 | Cardiac Pacemakers Inc. | Method and device for electrochemical formation of therapeutic species in vivo |
US20050178584A1 (en) * | 2002-01-22 | 2005-08-18 | Xingwu Wang | Coated stent and MR imaging thereof |
WO2003071384A2 (en) * | 2002-02-15 | 2003-08-28 | Eunoe, Inc. | Systems and methods for flow detection and measurement in csf shunts |
US7261733B1 (en) * | 2002-06-07 | 2007-08-28 | Endovascular Technologies, Inc. | Endovascular graft with sensors design and attachment methods |
US7488345B2 (en) * | 2002-06-07 | 2009-02-10 | Endovascular Technologies, Inc. | Endovascular graft with pressor and attachment methods |
US7025778B2 (en) | 2002-06-07 | 2006-04-11 | Endovascular Technologies, Inc. | Endovascular graft with pressure, temperature, flow and voltage sensors |
US7065409B2 (en) * | 2002-12-13 | 2006-06-20 | Cardiac Pacemakers, Inc. | Device communications of an implantable medical device and an external system |
US7009511B2 (en) | 2002-12-17 | 2006-03-07 | Cardiac Pacemakers, Inc. | Repeater device for communications with an implantable medical device |
US7127300B2 (en) * | 2002-12-23 | 2006-10-24 | Cardiac Pacemakers, Inc. | Method and apparatus for enabling data communication between an implantable medical device and a patient management system |
US7395117B2 (en) * | 2002-12-23 | 2008-07-01 | Cardiac Pacemakers, Inc. | Implantable medical device having long-term wireless capabilities |
US6978182B2 (en) * | 2002-12-27 | 2005-12-20 | Cardiac Pacemakers, Inc. | Advanced patient management system including interrogator/transceiver unit |
US20040128161A1 (en) * | 2002-12-27 | 2004-07-01 | Mazar Scott T. | System and method for ad hoc communications with an implantable medical device |
EP1610740A4 (en) | 2003-04-04 | 2009-04-08 | Theken Disc Llc | Artificial disc prosthesis |
US20050119573A1 (en) * | 2003-11-05 | 2005-06-02 | Boris Vilenkin | Method and system for quantification of arterial stenosis |
US8060207B2 (en) | 2003-12-22 | 2011-11-15 | Boston Scientific Scimed, Inc. | Method of intravascularly delivering stimulation leads into direct contact with tissue |
US20050137646A1 (en) * | 2003-12-22 | 2005-06-23 | Scimed Life Systems, Inc. | Method of intravascularly delivering stimulation leads into brain |
US7295875B2 (en) * | 2004-02-20 | 2007-11-13 | Boston Scientific Scimed, Inc. | Method of stimulating/sensing brain with combination of intravascularly and non-vascularly delivered leads |
US9380980B2 (en) * | 2004-03-05 | 2016-07-05 | Depuy International Limited | Orthpaedic monitoring system, methods and apparatus |
US7590454B2 (en) | 2004-03-12 | 2009-09-15 | Boston Scientific Neuromodulation Corporation | Modular stimulation lead network |
US20050203600A1 (en) | 2004-03-12 | 2005-09-15 | Scimed Life Systems, Inc. | Collapsible/expandable tubular electrode leads |
US7177702B2 (en) | 2004-03-12 | 2007-02-13 | Scimed Life Systems, Inc. | Collapsible/expandable electrode leads |
US8353896B2 (en) | 2004-04-19 | 2013-01-15 | The Invention Science Fund I, Llc | Controllable release nasal system |
US20070010868A1 (en) * | 2004-04-19 | 2007-01-11 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Lumenally-active device |
US7857767B2 (en) * | 2004-04-19 | 2010-12-28 | Invention Science Fund I, Llc | Lumen-traveling device |
US8092549B2 (en) | 2004-09-24 | 2012-01-10 | The Invention Science Fund I, Llc | Ciliated stent-like-system |
US8512219B2 (en) | 2004-04-19 | 2013-08-20 | The Invention Science Fund I, Llc | Bioelectromagnetic interface system |
US8024036B2 (en) | 2007-03-19 | 2011-09-20 | The Invention Science Fund I, Llc | Lumen-traveling biological interface device and method of use |
US7998060B2 (en) * | 2004-04-19 | 2011-08-16 | The Invention Science Fund I, Llc | Lumen-traveling delivery device |
US7850676B2 (en) * | 2004-04-19 | 2010-12-14 | The Invention Science Fund I, Llc | System with a reservoir for perfusion management |
US8361013B2 (en) | 2004-04-19 | 2013-01-29 | The Invention Science Fund I, Llc | Telescoping perfusion management system |
US8337482B2 (en) * | 2004-04-19 | 2012-12-25 | The Invention Science Fund I, Llc | System for perfusion management |
US9011329B2 (en) * | 2004-04-19 | 2015-04-21 | Searete Llc | Lumenally-active device |
US20050234440A1 (en) * | 2004-04-19 | 2005-10-20 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | System with a sensor for perfusion management |
US8412348B2 (en) * | 2004-05-06 | 2013-04-02 | Boston Scientific Neuromodulation Corporation | Intravascular self-anchoring integrated tubular electrode body |
JP4977020B2 (en) | 2004-07-08 | 2012-07-18 | シェンバーガー,デボラ | Strain monitoring system and apparatus |
US7286879B2 (en) | 2004-07-16 | 2007-10-23 | Boston Scientific Scimed, Inc. | Method of stimulating fastigium nucleus to treat neurological disorders |
US20060064142A1 (en) | 2004-09-17 | 2006-03-23 | Cardiac Pacemakers, Inc. | Systems and methods for deriving relative physiologic measurements using an implanted sensor device |
US7918800B1 (en) | 2004-10-08 | 2011-04-05 | Endovascular Technologies, Inc. | Aneurysm sensing devices and delivery systems |
US8150509B2 (en) * | 2004-10-21 | 2012-04-03 | Cardiac Pacemakers, Inc. | Systems and methods for drug therapy enhancement using expected pharmacodynamic models |
US20060089856A1 (en) * | 2004-10-21 | 2006-04-27 | Cardiac Pacemakers | Integrated pharmaceutical dispensing and patient management monitoring |
US7813808B1 (en) | 2004-11-24 | 2010-10-12 | Remon Medical Technologies Ltd | Implanted sensor system with optimized operational and sensing parameters |
US7937160B2 (en) * | 2004-12-10 | 2011-05-03 | Boston Scientific Neuromodulation Corporation | Methods for delivering cortical electrode leads into patient's head |
EP1835964B1 (en) * | 2004-12-21 | 2016-03-09 | EBR Systems, Inc. | Leadless cardiac system for pacing and arrhythmia treatment |
US7606621B2 (en) * | 2004-12-21 | 2009-10-20 | Ebr Systems, Inc. | Implantable transducer devices |
US7752059B2 (en) | 2005-07-05 | 2010-07-06 | Cardiac Pacemakers, Inc. | Optimization of timing for data collection and analysis in advanced patient management system |
US8840660B2 (en) | 2006-01-05 | 2014-09-23 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
US8078278B2 (en) * | 2006-01-10 | 2011-12-13 | Remon Medical Technologies Ltd. | Body attachable unit in wireless communication with implantable devices |
US8089029B2 (en) * | 2006-02-01 | 2012-01-03 | Boston Scientific Scimed, Inc. | Bioabsorbable metal medical device and method of manufacture |
JP2009529954A (en) * | 2006-03-14 | 2009-08-27 | マコ サージカル コーポレーション | Prosthetic device and system and method for implanting a prosthetic device |
US20070224244A1 (en) * | 2006-03-22 | 2007-09-27 | Jan Weber | Corrosion resistant coatings for biodegradable metallic implants |
US20080058785A1 (en) * | 2006-04-12 | 2008-03-06 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Autofluorescent imaging and target ablation |
US9198563B2 (en) | 2006-04-12 | 2015-12-01 | The Invention Science Fund I, Llc | Temporal control of a lumen traveling device in a body tube tree |
US7650185B2 (en) * | 2006-04-25 | 2010-01-19 | Cardiac Pacemakers, Inc. | System and method for walking an implantable medical device from a sleep state |
US7955268B2 (en) * | 2006-07-21 | 2011-06-07 | Cardiac Pacemakers, Inc. | Multiple sensor deployment |
US7908334B2 (en) * | 2006-07-21 | 2011-03-15 | Cardiac Pacemakers, Inc. | System and method for addressing implantable devices |
CA2659761A1 (en) | 2006-08-02 | 2008-02-07 | Boston Scientific Scimed, Inc. | Endoprosthesis with three-dimensional disintegration control |
CA2663271A1 (en) * | 2006-09-15 | 2008-03-20 | Boston Scientific Limited | Bioerodible endoprostheses and methods of making the same |
US8808726B2 (en) * | 2006-09-15 | 2014-08-19 | Boston Scientific Scimed. Inc. | Bioerodible endoprostheses and methods of making the same |
ES2368125T3 (en) | 2006-09-15 | 2011-11-14 | Boston Scientific Scimed, Inc. | BIOEROSIONABLE ENDOPROOTHESIS WITH BIOESTABLE INORGANIC LAYERS. |
EP2959925B1 (en) * | 2006-09-15 | 2018-08-29 | Boston Scientific Limited | Medical devices and methods of making the same |
WO2008036548A2 (en) | 2006-09-18 | 2008-03-27 | Boston Scientific Limited | Endoprostheses |
CA2663717A1 (en) * | 2006-09-18 | 2008-03-27 | Boston Scientific Limited | Controlling biodegradation of a medical instrument |
EP2079359A1 (en) * | 2006-09-29 | 2009-07-22 | Philometron, Inc. | Foreign body response detection in an implanted device |
EP2277563B1 (en) | 2006-12-28 | 2014-06-25 | Boston Scientific Limited | Bioerodible endoprostheses and method of making the same |
US20080171941A1 (en) * | 2007-01-12 | 2008-07-17 | Huelskamp Paul J | Low power methods for pressure waveform signal sampling using implantable medical devices |
EP2139556B1 (en) * | 2007-03-26 | 2014-04-23 | Remon Medical Technologies Ltd. | Biased acoustic switch for implantable medical device |
EP2155051A1 (en) * | 2007-06-14 | 2010-02-24 | Cardiac Pacemakers, Inc. | Intracorporeal pressure measurement devices and methods |
US8052745B2 (en) * | 2007-09-13 | 2011-11-08 | Boston Scientific Scimed, Inc. | Endoprosthesis |
DE102007048595B3 (en) * | 2007-10-10 | 2009-02-26 | Ruwisch, Dietmar, Dr. | Device for determining the anchoring state of an implanted endoprosthesis |
US20090143855A1 (en) * | 2007-11-29 | 2009-06-04 | Boston Scientific Scimed, Inc. | Medical Device Including Drug-Loaded Fibers |
US20100008970A1 (en) * | 2007-12-14 | 2010-01-14 | Boston Scientific Scimed, Inc. | Drug-Eluting Endoprosthesis |
US8041431B2 (en) * | 2008-01-07 | 2011-10-18 | Cardiac Pacemakers, Inc. | System and method for in situ trimming of oscillators in a pair of implantable medical devices |
US8301262B2 (en) * | 2008-02-06 | 2012-10-30 | Cardiac Pacemakers, Inc. | Direct inductive/acoustic converter for implantable medical device |
US8236046B2 (en) | 2008-06-10 | 2012-08-07 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis |
US20090312650A1 (en) * | 2008-06-12 | 2009-12-17 | Cardiac Pacemakers, Inc. | Implantable pressure sensor with automatic measurement and storage capabilities |
US8798761B2 (en) * | 2008-06-27 | 2014-08-05 | Cardiac Pacemakers, Inc. | Systems and methods of monitoring the acoustic coupling of medical devices |
US20100004733A1 (en) * | 2008-07-02 | 2010-01-07 | Boston Scientific Scimed, Inc. | Implants Including Fractal Structures |
US20100023091A1 (en) * | 2008-07-24 | 2010-01-28 | Stahmann Jeffrey E | Acoustic communication of implantable device status |
US7985252B2 (en) * | 2008-07-30 | 2011-07-26 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis |
EP2337609B1 (en) | 2008-08-14 | 2016-08-17 | Cardiac Pacemakers, Inc. | Performance assessment and adaptation of an acoustic communication link |
US8078440B2 (en) * | 2008-09-19 | 2011-12-13 | Smith & Nephew, Inc. | Operatively tuning implants for increased performance |
US8382824B2 (en) * | 2008-10-03 | 2013-02-26 | Boston Scientific Scimed, Inc. | Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides |
US8593107B2 (en) * | 2008-10-27 | 2013-11-26 | Cardiac Pacemakers, Inc. | Methods and systems for recharging an implanted device by delivering a section of a charging device adjacent the implanted device within a body |
US8267992B2 (en) * | 2009-03-02 | 2012-09-18 | Boston Scientific Scimed, Inc. | Self-buffering medical implants |
US8668732B2 (en) * | 2010-03-23 | 2014-03-11 | Boston Scientific Scimed, Inc. | Surface treated bioerodible metal endoprostheses |
CN117258169A (en) | 2016-07-07 | 2023-12-22 | 加州大学评议会 | Implant for stimulating tissue using ultrasound |
WO2019204769A1 (en) | 2018-04-19 | 2019-10-24 | Iota Biosciences, Inc. | Implants using ultrasonic communication for modulating splenic nerve activity |
AU2019255377A1 (en) | 2018-04-19 | 2020-11-26 | Iota Biosciences, Inc. | Implants using ultrasonic communication for neural sensing and stimulation |
CA3120296A1 (en) * | 2019-01-04 | 2020-07-09 | Michel M. Maharbiz | Ultrasound-based protocol for operating an implantable device |
AU2020217806A1 (en) | 2019-02-07 | 2021-08-26 | Nuvasive Specialized Orthopedics, Inc. | Ultrasonic communication in medical devices |
US11589901B2 (en) | 2019-02-08 | 2023-02-28 | Nuvasive Specialized Orthopedics, Inc. | External adjustment device |
Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4114606A (en) * | 1976-11-12 | 1978-09-19 | The Johns Hopkins University | Monitoring apparatus for resonant circuit intracranial pressure implants |
US5967986A (en) * | 1997-11-25 | 1999-10-19 | Vascusense, Inc. | Endoluminal implant with fluid flow sensing capability |
US5972029A (en) * | 1997-05-13 | 1999-10-26 | Fuisz Technologies Ltd. | Remotely operable stent |
US6015387A (en) * | 1997-03-20 | 2000-01-18 | Medivas, Llc | Implantation devices for monitoring and regulating blood flow |
Family Cites Families (18)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4227407A (en) | 1978-11-30 | 1980-10-14 | Cornell Research Foundation, Inc. | Volume flow measurement system |
US4352960A (en) * | 1980-09-30 | 1982-10-05 | Baptist Medical Center Of Oklahoma, Inc. | Magnetic transcutaneous mount for external device of an associated implant |
US5306644A (en) | 1988-09-29 | 1994-04-26 | Hewlett-Packard Company | Mass sensor method for measuring analytes in a sample |
US5305758A (en) | 1991-04-12 | 1994-04-26 | Tetrad Corporation | Ultrasonic apparatus for use in obtaining blood flow information |
US5358514A (en) | 1991-12-18 | 1994-10-25 | Alfred E. Mann Foundation For Scientific Research | Implantable microdevice with self-attaching electrodes |
NL9200207A (en) | 1992-02-05 | 1993-09-01 | Nedap Nv | IMPLANTABLE BIOMEDICAL SENSOR DEVICE, IN PARTICULAR FOR MEASUREMENT OF THE GLUCOSE CONCENTRATION. |
US5306294A (en) | 1992-08-05 | 1994-04-26 | Ultrasonic Sensing And Monitoring Systems, Inc. | Stent construction of rolled configuration |
SE9401402D0 (en) | 1994-04-25 | 1994-04-25 | Siemens Elema Ab | Medical implant |
SE9403188D0 (en) | 1994-09-22 | 1994-09-22 | Siemens Elema Ab | Magnetic field detector on a medical implant |
US5720771A (en) | 1995-08-02 | 1998-02-24 | Pacesetter, Inc. | Method and apparatus for monitoring physiological data from an implantable medical device |
US5663507A (en) | 1996-03-18 | 1997-09-02 | President And Fellows At Harvard College | Semiconductor piezoelectric strain measuring transducer |
FR2746565B1 (en) | 1996-03-22 | 1998-05-22 | Ela Medical Sa | DEVICE FOR RECEIVING SIGNALS FROM AN IMPLANTED ACTIVE MEDICAL APPARATUS |
US5749909A (en) * | 1996-11-07 | 1998-05-12 | Sulzer Intermedics Inc. | Transcutaneous energy coupling using piezoelectric device |
US5735887A (en) | 1996-12-10 | 1998-04-07 | Exonix Corporation | Closed-loop, RF-coupled implanted medical device |
WO1998029030A1 (en) | 1997-01-03 | 1998-07-09 | Biosense Inc. | Pressure-sensing stent |
US5807258A (en) * | 1997-10-14 | 1998-09-15 | Cimochowski; George E. | Ultrasonic sensors for monitoring the condition of a vascular graft |
US5891180A (en) * | 1998-04-29 | 1999-04-06 | Medtronic Inc. | Interrogation of an implantable medical device using audible sound communication |
US6015386A (en) * | 1998-05-07 | 2000-01-18 | Bpm Devices, Inc. | System including an implantable device and methods of use for determining blood pressure and other blood parameters of a living being |
-
1999
- 1999-03-24 US US09/275,311 patent/US6170488B1/en not_active Expired - Fee Related
-
2000
- 2000-03-23 EP EP00918272A patent/EP1162922A1/en not_active Withdrawn
- 2000-03-23 JP JP2000606150A patent/JP2002538934A/en not_active Withdrawn
- 2000-03-23 WO PCT/US2000/007637 patent/WO2000056241A1/en not_active Application Discontinuation
- 2000-03-23 CA CA002364853A patent/CA2364853A1/en not_active Abandoned
- 2000-03-23 AU AU39111/00A patent/AU3911100A/en not_active Abandoned
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4114606A (en) * | 1976-11-12 | 1978-09-19 | The Johns Hopkins University | Monitoring apparatus for resonant circuit intracranial pressure implants |
US6015387A (en) * | 1997-03-20 | 2000-01-18 | Medivas, Llc | Implantation devices for monitoring and regulating blood flow |
US5972029A (en) * | 1997-05-13 | 1999-10-26 | Fuisz Technologies Ltd. | Remotely operable stent |
US5967986A (en) * | 1997-11-25 | 1999-10-19 | Vascusense, Inc. | Endoluminal implant with fluid flow sensing capability |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8165677B2 (en) | 2004-07-09 | 2012-04-24 | Cardiac Pacemakers, Inc. | Method and apparatus of acoustic communication for implantable medical device |
US8082041B1 (en) | 2007-06-15 | 2011-12-20 | Piezo Energy Technologies, LLC | Bio-implantable ultrasound energy capture and storage assembly including transmitter and receiver cooling |
US8974366B1 (en) | 2012-01-10 | 2015-03-10 | Piezo Energy Technologies, LLC | High power ultrasound wireless transcutaneous energy transfer (US-TET) source |
Also Published As
Publication number | Publication date |
---|---|
US6170488B1 (en) | 2001-01-09 |
AU3911100A (en) | 2000-10-09 |
EP1162922A1 (en) | 2001-12-19 |
JP2002538934A (en) | 2002-11-19 |
CA2364853A1 (en) | 2000-09-28 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6170488B1 (en) | Acoustic-based remotely interrogated diagnostic implant device and system | |
US6206835B1 (en) | Remotely interrogated diagnostic implant device with electrically passive sensor | |
US6330885B1 (en) | Remotely interrogated implant device with sensor for detecting accretion of biological matter | |
JP4011631B2 (en) | Pressure sensitive stent | |
US6015387A (en) | Implantation devices for monitoring and regulating blood flow | |
JP4657713B2 (en) | Strain detection system | |
US6431175B1 (en) | System and method for directing and monitoring radiation | |
Mazzilli et al. | In-vitro platform to study ultrasound as source for wireless energy transfer and communication for implanted medical devices | |
US7582052B2 (en) | Implantable hearing aid actuator positioning | |
US20020103425A1 (en) | self-contained monitoring device particularly useful for monitoring physiological conditions | |
US20080262347A1 (en) | Method and apparatus for monitoring integrity of an implanted device | |
KR101602900B1 (en) | Apparatus and method for automatic transmission power adjustment for doppler radar | |
EP3223758A1 (en) | Wearable ultrasound device for signalling changes in human or animal body | |
US6308715B1 (en) | Ultrasonic detection of restenosis in stents | |
IL141755A (en) | Medical implant system | |
WO2000056210A1 (en) | Remotely interrogated diagnostic implant device with electrically passive sensor | |
CN109688902A (en) | Communication device and method | |
US20230277059A1 (en) | Systems and methods for monitoring implantable devices for detection of implant failure utilizing wireless in vivo micro sensors | |
WO2001012092A1 (en) | Remotely interrogated diagnostic implant device with electrically passive sensor | |
WO2002056761A2 (en) | Acoustic-based remotely interrrogated diagnostic implant device and system | |
US20010050087A1 (en) | Ultrasonic detection of restenosis in stents | |
WO2001037733A2 (en) | Implant loosening and fracture healing evaluation apparatus and method | |
Chiao | Batteryless wireless gastric implants | |
AU758015B2 (en) | Medical implant system | |
WO2021043481A1 (en) | Implantable electronic sensing system for measuring and monitoring medical parameters |
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 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 NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT TZ UA UG 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 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 BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG |
|
DFPE | Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101) | ||
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
ENP | Entry into the national phase |
Ref document number: 2364853 Country of ref document: CA Ref country code: CA Ref document number: 2364853 Kind code of ref document: A Format of ref document f/p: F |
|
WWE | Wipo information: entry into national phase |
Ref document number: 2000918272 Country of ref document: EP |
|
ENP | Entry into the national phase |
Ref country code: JP Ref document number: 2000 606150 Kind code of ref document: A Format of ref document f/p: F |
|
WWP | Wipo information: published in national office |
Ref document number: 2000918272 Country of ref document: EP |
|
REG | Reference to national code |
Ref country code: DE Ref legal event code: 8642 |
|
WWW | Wipo information: withdrawn in national office |
Ref document number: 2000918272 Country of ref document: EP |