WO2009006602A1 - Capteur de pression sans fil et procédé de fabrication d'un capteur de pression sans fil conçu pour être intégré dans un dispositif implantable - Google Patents

Capteur de pression sans fil et procédé de fabrication d'un capteur de pression sans fil conçu pour être intégré dans un dispositif implantable Download PDF

Info

Publication number
WO2009006602A1
WO2009006602A1 PCT/US2008/069217 US2008069217W WO2009006602A1 WO 2009006602 A1 WO2009006602 A1 WO 2009006602A1 US 2008069217 W US2008069217 W US 2008069217W WO 2009006602 A1 WO2009006602 A1 WO 2009006602A1
Authority
WO
WIPO (PCT)
Prior art keywords
substrate
pressure sensor
inductor
accordance
sheet
Prior art date
Application number
PCT/US2008/069217
Other languages
English (en)
Inventor
Anthony I. Nunez
Harry D. Rowland
Original Assignee
Endotronix, Inc.
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
Priority claimed from US12/167,109 external-priority patent/US7677107B2/en
Application filed by Endotronix, Inc. filed Critical Endotronix, Inc.
Publication of WO2009006602A1 publication Critical patent/WO2009006602A1/fr

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
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021—Measuring pressure in heart or blood vessels
    • A61B5/0215—Measuring pressure in heart or blood vessels by means inserted into the body
    • 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
    • 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
    • A61F2250/0002—Means for transferring electromagnetic energy to implants for data transfer

Definitions

  • the subject matter disclosed herein relates generally to a wireless pressure sensor and, more particularly, to methods for fabricating wireless pressure sensors and integrating the wireless pressure sensors with an implantable device, such as an endovascular stent or graft.
  • a method for fabricating a wireless pressure sensor includes providing a first substrate. A portion of the first substrate is controllably displaced to form a cavity. A conducting material is patterned on the first substrate to form a first capacitor plate and a first inductor. A second substrate is provided. A conducting material is patterned on the second substrate to form a second capacitor plate. The second substrate is attached to the first substrate to seal the cavity such that at least a portion of the second substrate is movable with respect to the first substrate within the cavity in response to a change in an external condition.
  • a wireless pressure sensor in another aspect, includes a first substrate that defines a cavity. A first conducting material is patterned on the first substrate. The patterned conducting material forms a first capacitor plate and a first inductor. A second substrate is coupled to the first substrate. A second conducting material is patterned on the second substrate. The patterned conducting material forms a second capacitor plate. The second substrate is coupled to the first substrate to seal the cavity such that at least a portion of the second substrate is movable with respect to the first substrate within the cavity in response to a change in an external condition. [0004] In yet another aspect, a method for fabricating a flexible sheet of wireless sensors is provided. The method includes providing a first substrate.
  • a plurality of portions of the first substrate are controllably displaced to form a plurality of cavities.
  • a conducting material is patterned to form a plurality of corresponding first capacitor plates and corresponding first inductors.
  • a second substrate is provided.
  • a conducting material is patterned on the second substrate to form a plurality of second capacitor plates.
  • the second substrate is attached to the first substrate to seal each cavity such that at least a portion of the second substrate is movable with respect to the first substrate within the cavity in response to a change in an external condition.
  • a method for fabricating an endovascular implant from a sheet of flexible material including at least one wireless sensor.
  • the method includes providing a sheet of flexible material. Conductive traces are patterned diagonally across the sheet of flexible material such that when the flexible sheet is positioned about a tubular cylindrical mold structure, the conductive traces are aligned to create an inductor coil. Alternatively, the conductive traces may form a continuous inductor coil not fully wrapped around the mold structure.
  • At least one sensor is affixed to the sheet of flexible material, the at least one sensor electrically connected to the inductor coil.
  • the sheet of flexible material is wrapped about the tubular cylindrical mold structure such that the inductor coil wraps circumferentially around the sheet of flexible material. Additional sheets of flexible material may cover the inductor coil and the at least one sensor such that the inductor coil and the at least one sensor are not readily exposed to bodily fluids.
  • Figures 1-6 are schematic partial section view illustrating an exemplary system and method for fabricating one or more wireless pressure sensors
  • Figures 7-14 are schematic partial section view illustrating an alternative exemplary system and method for fabricating one or more wireless pressure sensors;
  • Figures 15-19 are schematic partial section view illustrating an exemplary system and method for electrically connecting or inductively coupling one or more inductors to a wireless pressure sensor;
  • Figures 20-23 illustrate an exemplary method for fabricating a sheet of wireless pressure sensors
  • Figure 24 shows an exemplary intraluminal graft with an integrated pressure sensor
  • Figures 25 and 26 show an exemplary intraluminal graft with an integrated pressure sensor having an inductor coil.
  • the present disclosure describes exemplary systems and methods for fabricating one or more wireless sensors, such as one or more pressure sensors, from polymer substrates or rigid substrates and integrating at least one wireless sensor in an implantable endovascular device, such as an endovascular or intraluminal stent or graft.
  • one or more wireless sensors such as one or more pressure sensors
  • an implantable endovascular device such as an endovascular or intraluminal stent or graft.
  • FIGS 1-6 are schematic partial sectional views illustrating an exemplary system and method for fabricating one or more sensors, such as one or more wireless pressure sensors 100, from one or more suitable polymer substrates or one or more suitable rigid substrates.
  • wireless pressure sensor 100 includes a first polymer substrate 110.
  • Suitable polymer materials for first polymer substrate 110 include, without limitation, a non-porous or low porosity polymer, such as polytetrafluoroethylene, expanded polytetrafluoroethylene (ePTFE), such as an ePTFE having a reduced permeability as related to an increased cross-linking and a decreased intermodal distance, other suitable fluoropolymers, and/or any suitable polymer material known to those skilled in the art and guided by the teachings herein provided.
  • a master mold 112 is positioned with respect to first polymer substrate 110 and pressed into first polymer substrate 110, as shown in Figure 2, to controllably displace a portion of first polymer substrate 110 and mold or define a cavity 114 within first polymer substrate 110, as shown in Figure 3.
  • cavity 114 may be formed using any suitable process including, without limitation, a lithography and chemical etching, an ink jet printing, and/or a laser writing process known to those skilled in the art and guided by the teachings herein provided.
  • a pattern of electrically conducting material including a first patterned capacitor plate 116 is layered or deposited on a surface 118 of first polymer substrate 110, as shown in Figure 4.
  • a hermetically sealed capacitive pressure sensor may reside in cavity 114 above first patterned capacitor plate 116.
  • first patterned capacitor plate 116 resides on an outer surface of a hermetically sealed capacitive pressure sensor.
  • a hermetically sealed capacitive pressure sensor may reside in cavity 114 between first polymer substrate 110 and second substrate 124. At least a portion of the hermetically sealed capacitive pressure sensor is movable in response to a change in an external condition.
  • references to a "hermetically sealed capacitive pressure sensor" may also refer to a hermetically sealed chamber with a deflectable membrane, wherein the hermetically sealed chamber may have electrically conducting areas on one or more surfaces.
  • a pattern of electrically conducting material including an inductor 120 electrically connected to a second patterned capacitor plate 122 is layered onto a second polymer substrate 124.
  • second polymer substrate 124 includes a suitable polymer material such as described above in reference to first polymer substrate 110.
  • Second polymer substrate 124 may be formed of the same polymer material or a different polymer material as the polymer material forming first polymer substrate 110.
  • Second polymer substrate 124, including inductor 120 and second patterned capacitor plate 122, is attached to first polymer substrate 110 to hermetically seal cavity 114.
  • a hermetically sealed capacitive pressure sensor may reside in cavity 114 between first polymer substrate 110 and second polymer substrate 124.
  • First patterned capacitor plate 116 and/or second patterned capacitor plate 122 may be mechanically and electrically coupled to the hermetically sealed capacitive pressure sensor.
  • the hermetically sealed capacitive pressure sensor may have capacitor plates on external surfaces that may be mechanically or electrically coupled to inductor 120. At least a portion of the hermetically sealed capacitive pressure sensor is movable in response to a change in an external condition.
  • first polymer substrate 110 and second polymer substrate 124 are axially aligned and laminated to form wireless pressure sensor 100 with second polymer substrate 124 directly above cavity 114.
  • second polymer substrate 124 includes a membrane that is movable toward first polymer substrate 110 in response to a change in an external condition.
  • first polymer substrate 110 and second polymer substrate 124 are coated with one or more additional layers of non-porous or low-porosity materials on one or more surfaces such that when attached or laminated, first polymer substrate 110 and second polymer substrate 124 form a hermetically sealed cavity 114.
  • Second polymer substrate 124 may be attached or coupled to first polymer substrate 110 using any suitable process including, without limitation, an adhesive bonding, laminating, and/or laser welding process.
  • inductor 120 on second polymer substrate 124 is electrically connected to first patterned capacitor plate 116 on first polymer substrate 110 during the attachment process.
  • inductor 120 may reside on a separate plane or surface than second patterned capacitor plate 122.
  • one or more surfaces of pressure sensor 100 is textured with a controlled topography that includes features, such as undulations, raised regions or ridges and/or recessed regions or valleys, having suitable dimensions including a height, a width and/or a length, ranging from about 10 nanometers (nm) to about 100 microns ( ⁇ m) such that properties of blood flow at or near external surface 126 may be modified.
  • patterning external surface 126 may modify coagulation properties of pressure sensor 100 to prevent or limit endothelialization and reduce a risk of thrombosis and/or embolism.
  • Patterning external surface 126 may also modify flow properties of blood at or near external surface 126 to promote or reduce slip at or near external surface 126 to alter a laminar flow characteristic and/or a turbulent flow characteristic of blood flowing across pressure sensor 100.
  • the controlled topography may also form small wells that may be filled with a slow release polymer that has been impregnated with an anitmetabolite substance that inhibits cell division, such as Tacrolimus or Sirolimus. The filled wells may then be covered with a porous polymer layer to allow a time-controlled release of a drug.
  • external surface 126 of pressure sensor 100 may be coated with a deactivated heparin bonded material having anti-coagulation and/or antimetabolite characteristics.
  • Figures 1-6 is fabricated in rigid substrates, such as a fused silica, glass, or high resistivity silicon material. Cavities are formed or defined in the rigid substrates using a suitable process known to those skilled in the art and guided by the teachings herein provided including, without limitation, a wet or dry chemical etch process. The surfaces may be patterned with electrically conducting material in a similar manner to the patterning on polymer substrates, as described above.
  • the rigid substrates may be attached or coupled using any suitable process including, without limitation, a fusion bonding, anodic bonding, laser welding, and/or adhesive sealing process.
  • a hermetically sealed capacitive pressure sensor may reside in the cavity between the first substrate and second substrate. At least a portion of the hermetically sealed capacitive pressure sensor is movable in response to a change in an external condition.
  • FIGS 7-14 are schematic partial sectional views illustrating an alternative exemplary system and method for fabricating one or more sensors, such as one or more wireless pressure sensors 200, from one or more suitable polymer substrates or one or more suitable rigid substrates.
  • wireless pressure sensor 200 includes a first polymer substrate 210.
  • Suitable polymer materials for first polymer substrate 210 include, without limitation, a non-porous or low porosity polymer, such as polytetrafluoroethylene, expanded polytetrafluoroethylene (ePTFE), such as an ePTFE having a reduced permeability as related to an increased cross-linking and a decreased intermodal distance, other suitable fluoropolymers, and/or any suitable polymer material known to those skilled in the art and guided by the teachings herein provided.
  • a master mold 212 is positioned with respect to first polymer substrate 210 and pressed into first polymer substrate 210, as shown in Figure 8, to mold or define a cavity 214 within first polymer substrate 210, as shown in Figure 9.
  • cavity 214 is formed using any suitable process including, without limitation, a lithography and chemical etching, an ink jet printing, and/or a laser writing process known to those skilled in the art and guided by the teachings herein provided.
  • a pattern of electrically conducting material including a first patterned capacitor plate 216 electrically connected to a first inductor 218 is layered or deposited on a surface 220 of first polymer substrate 210, as shown in Figure 10.
  • first inductor 218 may reside on a separate plane or surface than first patterned capacitor plate 216.
  • a hermetically sealed capacitive pressure sensor may reside in cavity 214. At least a portion of the hermetically sealed capacitive pressure sensor is movable in response to a change in an external condition.
  • a pattern of electrically conducting material including a second patterned capacitor plate 226 electrically connected to a second inductor 228 is layered onto a surface 230 of a second polymer substrate 232.
  • second polymer substrate 232 includes a suitable polymer material such as described above in reference to first polymer substrate 210.
  • Second polymer substrate 232 may be formed of the same polymer material or a different polymer material as the polymer material forming first polymer substrate 210.
  • Second polymer substrate 232, including second patterned capacitor plate 226 and second inductor 228, is attached or coupled to first polymer substrate 210 to hermetically seal cavity 214.
  • first polymer substrate 210 and second polymer substrate 232 are axially aligned and laminated to form wireless pressure sensor 200 with second polymer substrate 232 directly above cavity 214.
  • second polymer substrate 232 includes a membrane that is movable toward first polymer substrate 210 in response to a change in an external condition.
  • first polymer substrate 210 and/or second polymer substrate 232 are coated with one or more additional layers of non-porous or low-porosity material on one or more surfaces such that when attached or laminated, first polymer substrate 210 and second polymer substrate 232 form hermetically sealed cavity 214.
  • Second polymer substrate 232 may be attached or coupled to first polymer substrate 210 using any suitable process including, without limitation, an adhesive bonding, laminating, and/or laser welding process.
  • second inductor 228 on second polymer substrate 232 is electrically connected to first patterned capacitor plate 216 on first polymer substrate 210 during the attachment process.
  • a hermetically sealed capacitive pressure sensor may reside in cavity 214.
  • First patterned capacitor plate 216 and/or second patterned capacitor plate 226 may be mechanically and electrically coupled to the hermetically sealed capacitive pressure sensor.
  • the hermetically sealed capacitive pressure sensor may have capacitor plates on external surfaces that may be mechanically or electrically coupled at least to first inductor 218 or second inductor 228.
  • second patterned capacitor plate 226 and/or second inductor 228 may reside outside cavity 214 on an external surface of second polymer substrate 232.
  • the electrically conducting material on the external surface of second polymer substrate 232 may allow for tuning of sensor electrical properties after fabrication.
  • additional layers of polymer or other suitable materials may coat the external surface of second polymer substrate 232.
  • one or more additional polymer substrates such as a third polymer substrate 240 and a fourth polymer substrate 242 are provided.
  • third polymer substrate 240 and fourth polymer substrate 242 have an electrically conducting layer forming a third inductor 244 and a fourth inductor 246, respectively.
  • third polymer substrate 240 and/or fourth polymer substrate 242 includes a suitable polymer material such as described above in reference to first polymer substrate 210.
  • Third polymer substrate 240 and/or fourth polymer substrate 242 may be formed of the same polymer material or a different polymer material as the polymer material forming first polymer substrate 210 and/or second polymer substrate 232.
  • third polymer substrate 240 is attached or laminated to first polymer substrate 210 in axial alignment and fourth polymer substrate 242 is attached or coupled to third polymer substrate 240 in axial alignment such that third inductor 244 and fourth inductor 246 are inductively coupled to inductor 218 formed on first polymer substrate 210 and second inductor 228 formed on second polymer substrate 232.
  • third inductor 244 and fourth inductor 246 are electrically connected to each other and to first inductor 218 to form three inductors electrically connected in a series circuit.
  • the inductors may be on one or more surfaces of the polymer substrates.
  • the inductors are electrically connected in series by electrical vias.
  • Third polymer substrate 240 and fourth polymer substrate 242 may be attached or coupled to pressure sensor 200 using any suitable process including, without limitation, an adhesive bonding, laminating, and/or laser welding process.
  • one or more surfaces of pressure sensor 200 is textured with a controlled topography that includes features, such as undulations, raised regions or ridges and/or recessed regions or valleys, having suitable dimensions including a height, a width and/or a length, ranging from about 10 nm to about 100 ⁇ m such that properties of blood flow at or near external surface 250 may be modified.
  • patterning external surface 250 may modify coagulation properties of pressure sensor 200 to prevent or limit endothelialization and reduce a risk of thrombosis and/or embolism.
  • Patterning external surface 250 may also modify flow properties of blood at or near external surface 250 to promote or reduce slip at or near external surface 250 to alter a laminar flow characteristic and/or a turbulent flow characteristic of blood flowing across pressure sensor 200.
  • the controlled topography may also form small wells that may be filled with a slow release polymer that has been impregnated with an anitmetabolite substance that inhibits cell division, such as Tacrolimus or Sirolimus. The filled wells may then be covered with a porous polymer layer to allow a time- controlled release of a drug.
  • external surface 250 of pressure sensor 200 may be coated with a deactivated heparin bonded material having anticoagulation and/or antimetabolite characteristics.
  • pressure sensor 200 shown in Figures 7-14 is fabricated in rigid substrates, such as a fused silica, glass, or high resistivity silicon material. Cavities are formed or defined in the rigid substrates using a suitable process known to those skilled in the art and guided by the teachings herein provided including, without limitation, a wet or dry chemical etch process. The surfaces may be patterned with electrically conducting material in a similar manner to the patterning on polymer substrates, as described above. The rigid substrates may be attached or coupled using any suitable process including, without limitation, a fusion bonding, anodic bonding, laser welding, and/or adhesive sealing process.
  • a hermetically sealed capacitive pressure sensor may reside in the cavity between the first substrate and the second substrate. At least a portion of the hermetically sealed capacitive pressure sensor is movable in response to a change in an external condition.
  • Figures 15-19 are schematic partial sectional views illustrating an alternative exemplary system and method for fabricating one or more sensors, such as pressure sensor 300, including one or more inductors electrically connected or inductively coupled to pressure sensor 300.
  • pressure sensor 300 includes a first polymer substrate 310, as shown in Figure 19.
  • Suitable polymer materials for first polymer substrate 310 include, without limitation, a non-porous or low porosity polymer, such as polytetrafluoroethylene, expanded polytetrafiuoroethylene, other suitable fluoropolymers, and/or any suitable polymer material known to those skilled in the art and guided by the teachings herein provided.
  • First polymer substrate 310 defines a cavity 314 within first polymer substrate 310, as shown in Figure 19. Cavity 314 is formed using any suitable process such as described above in reference to cavity 114 and/or cavity 214.
  • a pattern of electrically conducting material including a first patterned capacitor plate 316 electrically connected to a first inductor 318 is layered or deposited on a surface 320 of first polymer substrate 310.
  • a pattern of electrically conducting material including a second patterned capacitor plate 326 electrically connected to a second inductor 328 is layered onto a surface 330 of a second polymer substrate 332.
  • second polymer substrate 332 includes a suitable polymer material such as described above in reference to first polymer substrate 310.
  • Second polymer substrate 332 may be formed of the same polymer material or a different polymer material as the polymer material forming first polymer substrate 310.
  • Second polymer substrate 332, including second patterned capacitor plate 326 and second inductor 328, is attached or coupled to first polymer substrate 310 to hermetically seal cavity 314.
  • first polymer substrate 310 and second polymer substrate 332 are axially aligned and laminated to form wireless pressure sensor 300 with second polymer substrate 332 directly above cavity 314.
  • a hermetically sealed capacitive pressure sensor may reside in cavity 314 between first polymer substrate 310 and second polymer substrate 332. At least a portion of the hermetically sealed capacitive pressure sensor is movable in response to a change in an external condition.
  • second polymer substrate 332 includes a membrane that is movable toward first polymer substrate 310 in response to a change in an external condition.
  • first polymer substrate 310 and/or second polymer substrate 332 are coated with one or more additional layers of non- porous or low-porosity material on one or more surfaces such that when attached or laminated, first polymer substrate 310 and second polymer substrate 332 form hermetically sealed cavity 314.
  • Second polymer substrate 332 may be attached or coupled to first polymer substrate 310 using any suitable process including, without limitation, an adhesive bonding, laminating, and/or laser welding process.
  • second inductor 328 on second polymer substrate 332 is electrically connected to first capacitor plate 316 on first polymer substrate 310 during the attachment process.
  • pressure sensor 300 includes a third polymer substrate 340, as shown in Figure 15.
  • third polymer substrate 340 includes a suitable polymer material such as described above in reference to first polymer substrate 310 and/or second polymer substrate 332.
  • Third polymer substrate 340 may be formed of the same polymer material or a different polymer material as the polymer material forming first polymer substrate 310 and/or second polymer substrate 332.
  • a master mold 342 is positioned with respect to third polymer substrate 340 and pressed into third polymer substrate 340, as shown in Figure 16, to mold or define a cavity 344 within third polymer substrate 340, as shown in Figure 17.
  • cavity 344 is formed using any suitable process including, without limitation, a lithography and chemical etching, an ink jet printing, and/or a laser writing process known to those skilled in the art and guided by the teachings herein provided.
  • a layer of patterned electrically conducting material including a third inductor 350 is deposited in cavity 344 of third polymer substrate 340, as shown in Figure 18.
  • a fourth polymer substrate 360 including a fourth inductor 370 is formed.
  • Third polymer substrate 340 with patterned third inductor 350 and fourth polymer substrate 360 are then attached or coupled to pressure sensor 300 in axial alignment such that third inductor 350 and fourth inductor 370 are inductively coupled to first inductor 318 and second inductor 328.
  • third inductor 350 is electrically connected to fourth inductor 370 and to first inductor 318 to form three inductors electrically connected in a series circuit.
  • Third polymer substrate 340 and fourth polymer substrate 360 may be attached or coupled to pressure sensor 300 using any suitable process including, without limitation, an adhesive bonding, laminating, and/or laser welding process.
  • pressure sensor 300 includes a third polymer substrate and a fourth substrate formed of a rigid material, such as a fused silica, glass, or high resistivity silicon material. Cavities are formed or defined in the rigid substrates using a suitable wet or dry chemical etch process known to those skilled in the art and guided by the teachings herein provided. The surfaces are patterned with electrically conducting material in a similar manner to the patterning on polymer substrates, as described above.
  • the rigid substrates may be attached or coupled using any suitable process including, without limitation, a fusion bonding, anodic bonding, laser welding, and/or adhesive sealing process.
  • Figures 20-23 show an exemplary sheet of sensors.
  • a number of individual sensors such as wireless pressure sensors 400, are affixed or attached to the sheet using an adhesive.
  • the sheet is heated and pressure sensors 400 are pressed into the heated sheet such that the sheet melts and cools around pressure sensors 400 to bind pressure sensors 400 to the sheet.
  • the individual pressure sensors 400 may be flexible polymer sensors or rigid sensors fabricated from a fused silica, glass, or high resistivity silicon material.
  • the individual pressure sensors 400 may be rigid hermetically sealed capacitive pressure sensors that are electrically connected or inductively coupled to electrically conducting elements on the flexible sheets of polymer.
  • the electrically conducting elements may be directed towards the external surfaces of the bound pressure sensor sheets or the internal surfaces of the bound pressure sensor sheets. Additional coatings and/or layers may be applied to the external surfaces of the bound pressure sensor sheets.
  • a plurality of hermetically sealed capacitive pressure sensors may reside in the cavity between the first substrate and second substrate.
  • the hermetically sealed chamber may be rigid while the remaining portions of the sheet of wireless sensors are flexible. At least a portion of the hermetically sealed capacitive pressure sensors is movable in response to a change in an external condition.
  • a polymer sheet 402 includes a plurality of polymer wireless pressure sensors 400.
  • Polymer sheet 402 is made of any suitable polymer material, such as described above.
  • Pressure sensors 400 are fabricated directly into polymer sheet 402.
  • a plurality of cavities 404 are formed or defined in polymer sheet 402 using a suitable process including, without limitation, a molding, embossing, lithography and chemical etching, ink jet printing, and/or laser writing process known to those skilled in the art and guided by the teachings herein provided.
  • a hermetically sealed capacitive pressure sensor may reside in one or more cavities 404. At least a portion of the hermetically sealed capacitive pressure sensor is movable in response to a change in an external condition.
  • Polymer sheet 402 is patterned with electrically conducting material including a first patterned capacitor plate 406 electrically connected to a first inductor 408.
  • Figure 21 shows a cross- sectional view of a portion of patterned polymer sheet 400 along a sectional line 410 of Figure 20 forming a portion of one pressure sensor 400.
  • a second polymer sheet 420 is patterned with electrically conducting material including a second patterned capacitor plate 422 electrically connected to a second inductor 424.
  • Figure 23 shows a cross- sectional view of a portion of patterned second polymer sheet 420 along a sectional line 426 of Figure 20 forming a portion of one pressure sensor 400.
  • a sheet of polymer pressure sensors 400 is formed by coupling or attaching first polymer sheet 402 with first patterned capacitor plates 406 and first inductors 408 to second polymer sheet 420 with second patterned capacitor plates 422 and second inductors 424.
  • first patterned capacitor plates 406 are axially aligned with corresponding second patterned capacitor plates 422 and first inductors 408 axially aligned with corresponding second inductors 424.
  • First polymer sheet 402 is attached or coupled to second polymer sheet 420 using any suitable process known to those skilled in the art and guided by the teachings herein provided including, without limitation, an adhesive bonding, laminating, and/or laser welding process.
  • first polymer sheet 402 and/or second polymer sheet 420 is coated with a suitable coating material or layer and/or sealed using a suitable sealing process to form hermetically sealed cavities.
  • additional polymer sheets including patterned inductors may be attached in axial alignment to first polymer sheet 402.
  • the additional inductors are electrically connected to each other and to corresponding first inductor 408 to form multiple inductors electrically connected in a series circuit for each polymer pressure sensor 400.
  • the additional inductors are not electrically connected but are inductively coupled.
  • the sheet of polymer pressure sensors 400 may be textured with a controlled topography including features, such as undulations, raised regions or ridges and/or recessed regions or valleys, having suitable dimensions including a height, a width and/or a length, ranging from about 10 nm to about 100 ⁇ m such that properties of blood flow at or near an exterior surface of pressure sensor 400 are modified. Patterning the exterior surface of pressure sensor 400 may modify coagulation properties of pressure sensor 400 to prevent or limit endothelialization and reduce a risk of thrombosis or embolism.
  • Patterning the exterior surface of pressure sensor 400 may also modify flow properties of blood at or near the exterior surface to promote or reduce slip at or near the exterior surface to alter a laminar flow characteristic and/or a turbulent flow characteristic of blood across pressure sensor 400.
  • the controlled topography may also form small wells that may be filled with a slow release polymer that has been impregnated with an anitmetabolite substance that inhibits cell division, such as Tacrolimus or Sirolimus. The filled wells may then be covered with a porous polymer layer to allow a time- controlled release of a drug.
  • the external surface of pressure sensor 400 may be coated with a deactivated heparin bonded material having anticoagulation or antimetabolite characteristics.
  • the sheet of polymer sensors may be used to form an implantable endovascular or intraluminal device, such as a stent or graft.
  • the sheet of pressure sensors are formed into a tubular intraluminal graft having integrated sensors.
  • the integrated sensors face an interior surface and/or an exterior surface of the intraluminal graft.
  • the intraluminal graft includes the integrated sensors positioned on the luminal or inner surface of the intraluminal graft.
  • a tubular cylindrical mold structure is provided.
  • a wire is positioned or wrapped about at least a portion of the tubular cylindrical mold structure.
  • Second polymer sheet 420 including second patterned capacitor plates 422 and second inductors 424 are positioned about the tubular cylindrical mold structure to cover the wire and the tubular cylindrical mold structure.
  • First polymer sheet 402 including first patterned capacitor plates 406 and first inductors 408 is attached or coupled to second polymer sheet 420 to cover second polymer sheet 420.
  • one or more additional polymer sheets including additional patterned inductors are coupled or attached to first polymer sheet 402 such that the additional inductors are electrically connected or inductively coupled to inductors 408 on first polymer sheet 402. The wire and the polymer sheets are released from the tubular cylindrical mold structure.
  • the polymer sheets are attached in a reverse or opposite order to form an intraluminal graft including integrated sensors on an exterior surface of the intraluminal graft.
  • the intraluminal graft may be integrated with sensors on the exterior surface and the interior or luminal surface of the intraluminal graft.
  • multiple planar polymer sheets including integrated sensors are formed into an endovascular or intraluminal graft by wrapping the previously formed polymer sheets with integrated sensors around the tubular cylindrical mold structure.
  • a medical implant, 500 such as an intraluminal graft, including one or more integrated pressure sensors 502 is fabricated or formed from a first sheet 504 of a suitable flexible material.
  • First sheet 504 is patterned with conductive traces 506 that extend diagonally across a first dimension, such as a width, of first sheet 504 such that when first sheet 504 is molded or wrapped about a tubular cylindrical mold structure (not shown), conductive traces 506 are aligned at joined edges (not shown) to create an inductor coil 508 that extends circumferentially about an external surface of intraluminal graft 500.
  • conductive traces 506 may form a continuous inductor coil not fully wrapped around the mold structure.
  • pressure sensor 502 is a hermetically sealed capacitive pressure sensor.
  • pressure sensor 502 includes a micro- electromechanical systems (MEMS) capacitive pressure sensor that is attached or coupled to first sheet 504.
  • pressure sensor 502 includes an application specific integrated circuit (ASIC) with a hermetically sealed chamber, or a hermetically sealed chamber electrically connected or inductively coupled to an ASIC that does not include an integral sensor. At least a portion of the hermetically sealed pressure sensor is movable in response to a change in an external condition.
  • a suitable electrical connection 510 provides electrical communication between pressure sensor 502 and inductor coil 508.
  • First sheet 504 is molded or wrapped about the tubular cylindrical mold structure such that pressure sensor 502 is positioned on an exterior curved surface of intraluminal graft 500.
  • a conducting layer (not shown) is applied or deposited at the joint joining the opposing edges of first sheet 504 to ensure an electrical connection within inductor coil 508.
  • Pressure sensor 502 may be formed as a rigid unit affixed to first sheet 504 or may be formed as a capacitive pressure sensor, such as described herein.
  • an additional sheet of flexible material with a patterned capacitor plate is attached or coupled to first sheet 504 in axial alignment to a patterned capacitor plate on first sheet 504 to form a pressure sensor between the sheets of flexible material.
  • the pressure sensor is electrically connected to inductor coil 508 on first sheet 504.
  • Multiple layers of material may be attached or coupled on one or more surfaces of first sheet 504 to form a medical implant, such as an intraluminal graft, with a circumferentially positioned inductor coil that is electrically connected to one or more pressure sensors on an interior or luminal surface and/or an exterior surface of the medical implant.
  • the sheet of sensors provides a system to monitor an intraluminal graft.
  • a shape memory alloy such as a Nitinol material, may be integrated into the sheet of sensors to aid in compact endovascular delivery of the sheet of sensors to the monitoring site.
  • the sheet of sensors may be delivered to the endovascular monitoring site following a method including wrapping the sheet of sensors about a stent delivery mechanism such that the sheet of sensors is deployed prior to delivery of the stent.
  • the deployed sheet of sensors expands and unfurls with a cylindrical radius larger than a cylindrical radius of the deployed stent to avoid interference of the sheet of sensors with the stent.
  • the sheet of sensors may be delivered using any suitable delivery method known to those skilled in the art and guided by the teachings herein provided.
  • an outer sheath is withdrawn to deliver the sheet of sensors.
  • the sheet of sensors may be delivered by a translumbar deployment after placement of a stent, or the sheet of sensors may be delivered by a transfemoral deployment by an uncoiling of the sensors, wherein an inferior aspect of the roll is pulled to facilitate unwrapping or uncovering the sheet of sensors.
  • the sheet of sensors may be delivered by placing the sheet of sensors on a semirigid wire backbone that is passed through distal openings and proximal openings defined within the sheet of sensors and is detached by twisting or rotating. The wire backbone is then rotated and withdrawn.
  • Figures 25 and 26 schematically illustrate a method for forming a pressure sensor with an inductor coil 508 including patterning conductive traces 506 formed diagonally across first sheet 504 such that when first sheet 504 is molded or wrapped about the tubular cylindrical mold structure, conductive traces 506 are aligned at a joint that joins the opposing edges of first sheet 504 to form inductor coil 508.
  • a conductive site 510 is patterned on first sheet 504 to provide an electrical connection to a hermetically sealed pressure sensor that is electrically connected to conductive traces 506.
  • a conducting layer (not shown) is deposited at an edge of first sheet 504 to ensure electrical connection of inductor coil 508.
  • the capacitive pressure sensor 502 is attached or coupled to first sheet 504 and to inductor coil 508.
  • an external surface of first sheet 504 may be textured with features, such as undulations, raised regions or ridges and/or recessed regions or valleys, having suitable dimensions including a height, a width and/or a length, ranging from about 10 nm to about 100 ⁇ m such that properties of blood flow at or near the external surface of first sheet 504 are modified. Patterning the external surface of first sheet 504 may modify coagulation properties of first sheet 504 to prevent or limit endothelialization and reduce a risk of thrombosis and/or embolism.
  • Patterning the external surface may also modify flow properties of blood at or near the external surface to promote or reduce slip at or near the external surface to alter a laminar flow characteristic and/or a turbulent flow characteristic of blood through the intraluminal graft.
  • the controlled topography may also form small wells that may be filled with a slow release polymer that has been impregnated with an anitmetabolite substance that inhibits cell division, such as Tacrolimus or Sirolimus. The filled wells may then be covered with a porous polymer layer to allow a time- controlled release of a drug.
  • the external surface of the pressure sensor may be coated with a deactivated heparin bonded material having anti-coagulation or antimetabolite characteristics.

Abstract

La présente invention concerne un procédé de fabrication d'un capteur de pression sans fil. Le procédé consiste à utiliser un premier substrat dont une partie est déplacée de façon contrôlée afin de former une cavité, à appliquer un motif de matériau conducteur sur le premier substrat, afin de former une première plaque de condensateur et une première bobine d'induction, à utiliser un second substrat, à appliquer un motif de matériau conducteur sur le second substrat, afin de former une seconde plaque de condensateur, puis à relier le second substrat au premier substrat afin de sceller la cavité, de manière qu'au moins une partie du second substrat puisse se déplacer par rapport au premier substrat dans la cavité en réponse à une variation d'une condition externe. Un capteur de pression capacitif hermétiquement scellé peut se trouver dans la cavité, entre le premier substrat et le second substrat.
PCT/US2008/069217 2007-07-03 2008-07-03 Capteur de pression sans fil et procédé de fabrication d'un capteur de pression sans fil conçu pour être intégré dans un dispositif implantable WO2009006602A1 (fr)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US94790907P 2007-07-03 2007-07-03
US60/947,909 2007-07-03
US12/167,109 US7677107B2 (en) 2007-07-03 2008-07-02 Wireless pressure sensor and method for fabricating wireless pressure sensor for integration with an implantable device
US12/167,109 2008-07-02

Publications (1)

Publication Number Publication Date
WO2009006602A1 true WO2009006602A1 (fr) 2009-01-08

Family

ID=40221655

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2008/069217 WO2009006602A1 (fr) 2007-07-03 2008-07-03 Capteur de pression sans fil et procédé de fabrication d'un capteur de pression sans fil conçu pour être intégré dans un dispositif implantable

Country Status (1)

Country Link
WO (1) WO2009006602A1 (fr)

Cited By (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN104545795A (zh) * 2015-02-09 2015-04-29 中国科学院电子学研究所 平面电感与电容串联的无线连接眼压传感器
WO2016028581A1 (fr) * 2014-08-18 2016-02-25 St. Jude Medical, Cardiology Division, Inc. Dispositifs cardiaques prothétiques ayant des capacités de diagnostic
US9737264B2 (en) 2014-08-18 2017-08-22 St. Jude Medical, Cardiology Division, Inc. Sensors for prosthetic heart devices
US9808201B2 (en) 2014-08-18 2017-11-07 St. Jude Medical, Cardiology Division, Inc. Sensors for prosthetic heart devices
US10806352B2 (en) 2016-11-29 2020-10-20 Foundry Innovation & Research 1, Ltd. Wireless vascular monitoring implants
US10806428B2 (en) 2015-02-12 2020-10-20 Foundry Innovation & Research 1, Ltd. Implantable devices and related methods for heart failure monitoring
US11039813B2 (en) 2015-08-03 2021-06-22 Foundry Innovation & Research 1, Ltd. Devices and methods for measurement of Vena Cava dimensions, pressure and oxygen saturation
US11206992B2 (en) 2016-08-11 2021-12-28 Foundry Innovation & Research 1, Ltd. Wireless resonant circuit and variable inductance vascular monitoring implants and anchoring structures therefore
US11564596B2 (en) 2016-08-11 2023-01-31 Foundry Innovation & Research 1, Ltd. Systems and methods for patient fluid management
US11701018B2 (en) 2016-08-11 2023-07-18 Foundry Innovation & Research 1, Ltd. Wireless resonant circuit and variable inductance vascular monitoring implants and anchoring structures therefore
US11779238B2 (en) 2017-05-31 2023-10-10 Foundry Innovation & Research 1, Ltd. Implantable sensors for vascular monitoring
US11944495B2 (en) 2017-05-31 2024-04-02 Foundry Innovation & Research 1, Ltd. Implantable ultrasonic vascular sensor

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4531244A (en) * 1983-07-14 1985-07-30 Hamas Robert S Mammary prosthesis with multiple flow spaces
US6535116B1 (en) * 2000-08-17 2003-03-18 Joe Huayue Zhou Wireless vehicle monitoring system
US20050287287A1 (en) * 2004-06-24 2005-12-29 Parker Theodore L Methods and systems for loading an implantable medical device with beneficial agent
US6994666B2 (en) * 2001-06-05 2006-02-07 Edwards Lifesciences Corporation Non-porous smooth ventricular assist device conduit
US20070074579A1 (en) * 2005-10-03 2007-04-05 Honeywell International Inc. Wireless pressure sensor and method of forming same
WO2007041584A2 (fr) * 2005-10-03 2007-04-12 Combinatorx, Incorporated Capteurs implantables, pompes implantables et associations de medicaments empechant la formation de cicatrices

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4531244A (en) * 1983-07-14 1985-07-30 Hamas Robert S Mammary prosthesis with multiple flow spaces
US6535116B1 (en) * 2000-08-17 2003-03-18 Joe Huayue Zhou Wireless vehicle monitoring system
US6994666B2 (en) * 2001-06-05 2006-02-07 Edwards Lifesciences Corporation Non-porous smooth ventricular assist device conduit
US20050287287A1 (en) * 2004-06-24 2005-12-29 Parker Theodore L Methods and systems for loading an implantable medical device with beneficial agent
US20070074579A1 (en) * 2005-10-03 2007-04-05 Honeywell International Inc. Wireless pressure sensor and method of forming same
WO2007041584A2 (fr) * 2005-10-03 2007-04-12 Combinatorx, Incorporated Capteurs implantables, pompes implantables et associations de medicaments empechant la formation de cicatrices

Cited By (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2016028581A1 (fr) * 2014-08-18 2016-02-25 St. Jude Medical, Cardiology Division, Inc. Dispositifs cardiaques prothétiques ayant des capacités de diagnostic
US9737264B2 (en) 2014-08-18 2017-08-22 St. Jude Medical, Cardiology Division, Inc. Sensors for prosthetic heart devices
US9808201B2 (en) 2014-08-18 2017-11-07 St. Jude Medical, Cardiology Division, Inc. Sensors for prosthetic heart devices
US10433791B2 (en) 2014-08-18 2019-10-08 St. Jude Medical, Cardiology Division, Inc. Prosthetic heart devices having diagnostic capabilities
US10537287B2 (en) 2014-08-18 2020-01-21 St. Jude Medical, Cardiology Division, Inc. Sensors for prosthetic heart devices
CN104545795A (zh) * 2015-02-09 2015-04-29 中国科学院电子学研究所 平面电感与电容串联的无线连接眼压传感器
US10905393B2 (en) 2015-02-12 2021-02-02 Foundry Innovation & Research 1, Ltd. Implantable devices and related methods for heart failure monitoring
US10806428B2 (en) 2015-02-12 2020-10-20 Foundry Innovation & Research 1, Ltd. Implantable devices and related methods for heart failure monitoring
US11039813B2 (en) 2015-08-03 2021-06-22 Foundry Innovation & Research 1, Ltd. Devices and methods for measurement of Vena Cava dimensions, pressure and oxygen saturation
US11206992B2 (en) 2016-08-11 2021-12-28 Foundry Innovation & Research 1, Ltd. Wireless resonant circuit and variable inductance vascular monitoring implants and anchoring structures therefore
US11564596B2 (en) 2016-08-11 2023-01-31 Foundry Innovation & Research 1, Ltd. Systems and methods for patient fluid management
US11701018B2 (en) 2016-08-11 2023-07-18 Foundry Innovation & Research 1, Ltd. Wireless resonant circuit and variable inductance vascular monitoring implants and anchoring structures therefore
US10806352B2 (en) 2016-11-29 2020-10-20 Foundry Innovation & Research 1, Ltd. Wireless vascular monitoring implants
US11779238B2 (en) 2017-05-31 2023-10-10 Foundry Innovation & Research 1, Ltd. Implantable sensors for vascular monitoring
US11944495B2 (en) 2017-05-31 2024-04-02 Foundry Innovation & Research 1, Ltd. Implantable ultrasonic vascular sensor

Similar Documents

Publication Publication Date Title
US7677107B2 (en) Wireless pressure sensor and method for fabricating wireless pressure sensor for integration with an implantable device
WO2009006602A1 (fr) Capteur de pression sans fil et procédé de fabrication d'un capteur de pression sans fil conçu pour être intégré dans un dispositif implantable
US20090011117A1 (en) Methods for texturing a surface of an endovascular implant
US8506750B2 (en) Composite structure and process for producing the same
EP1726271B1 (fr) Manchon d'endoprothèse à adhérence sélective, mandrin de fabrication et procédé de fabrication de cette endoprothèse
JP4126003B2 (ja) フレキシブルｍｅｍｓトランスデューサとその製作方法及びこれを採用したフレキシブルｍｅｍｓ無線マイクロホン
US9492269B2 (en) Selective adherence of stent-graft coverings
JP5004426B2 (ja) 薬剤送出用ステント
EP2260792B1 (fr) Méthode de fabrication d'une endoprothèse vasculaire avec adhérence selective de la couche protectrice, ainsi que le mandrin utile à sa fabrication
Kiil et al. Scalable industrial manufacturing of DEAP
JP2009101170A (ja) Ｐｔｆｅ部品を備えたバルーン構造
EP2968666B1 (fr) Matériaux poreux possédant une microstructure fibrillaire et un revêtement fracturable
CA2666161A1 (fr) Greffons en eptfe a plusieurs bifurcations et protheses stent-greffon, et procede de fabrication
JP6208668B2 (ja) 破裂可能でかつ再シール可能なグラフト
EP2916883B1 (fr) Procédé de fabrication d'une prothèse stent-greffon avec deux couches de polytétrafluoroéthylène expansé
US20130199713A1 (en) Method for producing a medical device
Sridhar et al. A hydrogel-based wireless sensor using micromachined variable inductors with folded flex-circuit structures for biomedical applications
WO2023178106A1 (fr) Endoprothèse couverte avec couche imperméable élastomère
Sepúlveda et al. Design of a pressure sensor for post-EVAR surveillance

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 08781369

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 08781369

Country of ref document: EP

Kind code of ref document: A1