US20060107749A1 - Disposable wireless pressure sensor - Google Patents
Disposable wireless pressure sensor Download PDFInfo
- Publication number
- US20060107749A1 US20060107749A1 US10/995,460 US99546004A US2006107749A1 US 20060107749 A1 US20060107749 A1 US 20060107749A1 US 99546004 A US99546004 A US 99546004A US 2006107749 A1 US2006107749 A1 US 2006107749A1
- Authority
- US
- United States
- Prior art keywords
- layer
- idt
- piezoelectric
- dielectric
- polymer substrate
- Prior art date
- Legal status (The legal status 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 status listed.)
- Granted
Links
Images
Classifications
-
- 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
-
- 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
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01L—MEASURING FORCE, STRESS, TORQUE, WORK, MECHANICAL POWER, MECHANICAL EFFICIENCY, OR FLUID PRESSURE
- G01L9/00—Measuring steady of quasi-steady pressure of fluid or fluent solid material by electric or magnetic pressure-sensitive elements; Transmitting or indicating the displacement of mechanical pressure-sensitive elements, used to measure the steady or quasi-steady pressure of a fluid or fluent solid material, by electric or magnetic means
- G01L9/0001—Transmitting or indicating the displacement of elastically deformable gauges by electric, electro-mechanical, magnetic or electro-magnetic means
- G01L9/0008—Transmitting or indicating the displacement of elastically deformable gauges by electric, electro-mechanical, magnetic or electro-magnetic means using vibrations
- G01L9/0022—Transmitting or indicating the displacement of elastically deformable gauges by electric, electro-mechanical, magnetic or electro-magnetic means using vibrations of a piezoelectric element
- G01L9/0025—Transmitting or indicating the displacement of elastically deformable gauges by electric, electro-mechanical, magnetic or electro-magnetic means using vibrations of a piezoelectric element with acoustic surface waves
-
- 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
- A61B2560/04—Constructional details of apparatus
- A61B2560/0406—Constructional details of apparatus specially shaped apparatus housings
- A61B2560/0412—Low-profile patch shaped housings
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/02—Details of sensors specially adapted for in-vivo measurements
Definitions
- Embodiments are generally related to sensing devices and applications. Embodiments are also related to pressure sensor devices, systems and methods thereof. Embodiments are additionally related to disposable sensing devices based on piezoelectric polymer film materials. Embodiments are additionally related to medical devices for sensing bodily pressure based on fluid within a conduit.
- a variety of sensors can be utilized to detect conditions, such as pressure and temperature.
- the ability to detect pressure and/or temperature is an advantage to any device exposed to variable pressure conditions, which can be severely affected by these conditions.
- An example of such a device is a catheter, which of course, can experience variations in both temperature and pressure.
- Many different techniques have been proposed for sensing the pressure and/or temperature in catheters, and for delivering this information to an operator so that he or she is aware of pressure and temperature conditions associated with a catheter and any fluid, such as blood flowing therein.
- SAW Surface Acoustic Wave
- Pressure within a conduit can be measured utilizing a number of techniques. Perhaps the most common device for such measurement is a mechanical gauge, which can be coupled through one wall of the conduit to the fluid pressure within the conduit. Inside the gauge, a needle is deflected over a scale in proportion to the pressure within the conduit. In some instances, the standard pressure gauge may be replaced with a transducer, which converts pressure into an electrical signal, which is then monitored.
- a pressure sensor involves detecting a patient's blood pressure, and/or intracranial pressure.
- One typical method of monitoring blood pressure is to measure the fluid pressure within an intravenous tube, which is hydraulically coupled to the patient's vein.
- a catheter is inserted into the patient's vein and a plastic tube or conduit coupled to the catheter.
- a saline solution can be drip-fed through the plastic tubing or conduit to maintain a pressure balance against the pressure within the patient's vein.
- the saline fluid acts as a hydraulic fluid to cause the pressure within the plastic tubing to correspond to the pressure within the patient's vein.
- Various conventional SAW sensing devices are capable of measuring blood pressure.
- Such devices typically are configured from ceramic materials (like PZT), quartz-type piezoelectric materials or lithium niobate.
- Such devices are disadvantageous for medical applications, because the above-referenced materials utilized by such devices are inherently self-resonant, having extremely low piezoelectric coupling coefficient, expensive and difficult for micro-machining, and consequently, grossly reduce the possibility of making a low cost pressure sensor for medical applications.
- IDT interdigital transducer
- Disposable sensor systems and method are disclosed.
- a dielectric polymer substrate provided and a microstrip antenna formed upon the dielectric polymer substrate.
- a piezoelectric polymer layer e.g., a polyvinylidene fluoride (PVDF) piezoelectric film
- the microstrip antenna can be formed flexible in nature, which makes them suitable for conformal wraparound designs and applications.
- an interdigital (IDT) layer can be configured upon the PVDF piezoelectric layer, thereby permitting the piezoelectric polymer layer and the IDT layer to detect pressure data and transmit the data to a receiver via the antenna.
- a first bonding layer can be formed between the dielectric polymer substrate and the piezoelectric polymer layer.
- a second bonding layer can be formed between the IDT layer and the piezoelectric polymer layer.
- a protective cover layer can also be configured above the IDT layer.
- the IDT layer can be formed as a plurality of IDT finger electrodes, which may be configured from copper.
- the polymer substrate can include a gap formed centrally therein, such that the gap is filled with a gel comprising a low thermal conductivity and bio-compatible material.
- the polymer substrate is generally formed from a low thermal conductivity dielectric substrate material.
- FIG. 1 illustrates a side view of a disposable wireless pressure sensor system, which can be implemented in accordance with a preferred embodiment
- FIG. 2 illustrates a top view of the disposable wireless pressure sensor system depicted in FIG. 1 , in accordance with a preferred embodiment
- FIG. 3 illustrates a schematic diagram of a medical pressure sensing system, which can be implemented in accordance with an alternative embodiment
- FIG. 4 illustrates a schematic diagram of a microstrip antenna, which can be implemented in accordance with a preferred embodiment.
- FIG. 1 illustrates a side view of a disposable wireless pressure sensor system 100 , which can be implemented in accordance with a preferred embodiment.
- FIG. 2 illustrates a top view of the disposable wireless pressure sensor system 100 depicted in FIG. 1 , in accordance with a preferred embodiment. Note that in FIGS. 1-2 , identical or similar parts are generally indicated by identical reference numerals.
- System 100 generally includes a dielectric polymer substrate 102 .
- a microstrip antenna 104 can be formed upon the dielectric polymer substrate 102 . Additionally, a piezoelectric polymer layer 106 can be formed above the dielectric polymer substrate, while an interdigital (IDT) layer 108 can be configured upon the piezoelectric polymer layer 106 , thereby permitting the piezoelectric polymer layer 106 and the IDT layer 108 to detect pressure data and transmit the data to a receiver utilizing the antenna 104 .
- the piezoelectric polymer layer 106 can be configured as a thin sheet having a thickness in a range of 10-20 microns, depending upon design considerations.
- first bonding layer 114 can be formed between the dielectric polymer substrate 102 and the piezoelectric polymer layer 106 .
- a second bonding layer 112 can be formed between the IDT layer 108 and the piezoelectric polymer layer 106 .
- First and second bonding layers 114 and 112 function as adhesives.
- the adhesive material for bonding layers 114 , 112 can be, for example, cyano-acrylate or a similar material.
- the adhesive or bonding layer thickness for layers 114 , 112 can be in a range of approximately 10 to 20 micrometers depending of course upon design considerations.
- a protective cover layer 110 can be formed above the IDT layer.
- the protective cover layer 110 can be formed as a protective plastic sheet in order to ensure mechanical and chemical protection of system 100 as a whole.
- the IDT layer 108 can be configured to include IDT finger electrodes 116 , which are depicted in FIG. 2 .
- Each of the IDT finger electrodes 116 can be formed from copper.
- the copper IDT thickness can be for example, in a range of approximately 25 micrometers to 125 micrometers, depending upon design considerations. Note that in order to provide lower frequency capabilities, a winder line width, along with bigger device sizes thereof, the IDT finger electrodes can be printed on the piezoelectric polymer layer 106 , or can be electroplated or etched form a large sheet of IDT finger electrodes thereof.
- the dielectric polymer substrate 102 can also be configured to include a gap 120 filled with a gel 122 formed from a low thermal conductivity and biocompatible material.
- the piezoelectric polymer layer 106 can be configured as a polyvinylidene fluoride (PVDF) piezoelectric film, while the dielectric polymer substrate 102 can be formed from a low thermal conductivity dielectric substrate material. It is believed that the use of PVDF piezoelectric film in accordance with the preferred embodiment described herein can result in substantial cost-savings and increased sensor efficiency, particularly in medical pressure sensing applications.
- PVDF polyvinylidene fluoride
- system 100 can be particularly useful is the field of medical applications, such as blood pressure sensing.
- the PVDF piezoelectric film is therefore formed on the biocompatible low thermal conductivity dielectric polymer substrate 102 .
- the PVDF piezoelectric film changes with temperature and pressure. Utilizing a low thermal conductivity substrate, for example, the pyroelectric change by blood can be minimized.
- the antenna 104 can be printed on the dielectric polymer substrate.
- a number of transceivers can be provided including a piezoelectric polymer sheet material, which is less costly and much easier to work with than conventional pressure sensing devices.
- FIG. 3 illustrates a schematic diagram of a medical pressure sensing system 300 , which can be implemented in accordance with an alternative embodiment.
- sensor or system 100 of FIG. 1 is also depicted in FIG. 3 at a location relative to a conduit 301 , which can be implemented as, for example, a catheter through which fluid 303 flow, as indicated by arrows 302 and 304 .
- Fluid 303 can be, for example, blood.
- System or sensor 100 can therefore transmit and receive data to and from a transmitter/receiver 304 , which includes an antenna 306 . The wireless transmission of such data is indicated in FIG. 3 by arrows 308 .
- System 300 can therefore be utilized for measuring bodily fluid pressure within conduit 301 .
- FIG. 4 illustrates a schematic diagram of a microstrip antenna 400 , which can be implemented in accordance with a preferred embodiment.
- Microstrip antenna 400 generally includes a dielectric substrate 404 located above a ground plane 402 .
- a radiating patch 406 is generally disposed on or in substrate 404 .
- microstrip antenna 400 of FIG. 4 is analogous to microstrip antenna 104 of FIG. 1 .
- microstrip antenna 104 can be formed upon a dielectric polymer substrate 102 as indicated in FIG. 1 .
- substrate 102 of FIG. 1 is similar to substrate 404 of FIG. 4 .
- microstrip antenna 400 is suitable for adaptation to conformal wrap-around type designs and applications.
- Microstrip antennas, such as antenna 400 offer a number of advantages compared to conventional microwave antennas such as, for example light weight, low volume, and thin profile configurations, which can be made conformal; low fabrication cost; and readily amendable to mass production. Linear and circular polarizations are also possible with simple feed configurations. Additionally, dual-frequency and dual-polarization antennas can be easily constructed; because, no cavity backing is required and such devices can be easily integrated with microwave circuits.
Abstract
In general, a dielectric polymer substrate provided and an antenna formed upon the dielectric polymer substrate. A piezoelectric polymer layer (e.g., a polyvinylidene fluoride (PVDF) piezoelectric film) can be formed above the dielectric polymer substrate. Additionally, an interdigital (IDT) layer can be configured upon the PVDF piezoelectric layer, thereby permitting the piezoelectric polymer layer and the IDT layer to detect pressure data and transmit the data to a receiver via the antenna.
Description
- Embodiments are generally related to sensing devices and applications. Embodiments are also related to pressure sensor devices, systems and methods thereof. Embodiments are additionally related to disposable sensing devices based on piezoelectric polymer film materials. Embodiments are additionally related to medical devices for sensing bodily pressure based on fluid within a conduit.
- A variety of sensors can be utilized to detect conditions, such as pressure and temperature. The ability to detect pressure and/or temperature is an advantage to any device exposed to variable pressure conditions, which can be severely affected by these conditions. An example of such a device is a catheter, which of course, can experience variations in both temperature and pressure. Many different techniques have been proposed for sensing the pressure and/or temperature in catheters, and for delivering this information to an operator so that he or she is aware of pressure and temperature conditions associated with a catheter and any fluid, such as blood flowing therein.
- One type of sensor that has found wide use in pressure and temperature sensing applications is the Surface Acoustic Wave (SAW) sensor, which can be composed of a sense element on a base and pressure transducer sensor diaphragm that is part of the cover. For a SAW sensor to function properly, the sensor diaphragm should generally be located in intimate contact with the sense element at all pressure levels and temperatures.
- One of the problems with current SAW sensor designs, particularly those designs adapted to delicate pressure and temperature sensing applications, is the inability of conventional SAW sensing systems to meet the demand in low pressure applications. (e.g., 0 to 500 mmHg), while doing so in an efficient and low cost manner. Such systems are inherently expensive, awkward, and often are not reliable in accurately sensing air pressure and temperature. There is a continuing need to lower the cost of SAW sensor designs utilized in pressure and/or temperature sensing applications, particularly wireless pressure sensors.
- To lower the cost and raise efficiency, few components, less expensive materials and fewer manufacturing-processing steps are necessary. In order to achieve these goals, it is believed that a disposable SAW pressure sensor made of polymer substrate should be implemented, along with low cost processing steps. To date, such components have not been adequately achieved.
- One area where the ability to detect pressure and/or temperature is critically important is in the field of medical applications. Pressure within a conduit, for example, such as a catheter, can be measured utilizing a number of techniques. Perhaps the most common device for such measurement is a mechanical gauge, which can be coupled through one wall of the conduit to the fluid pressure within the conduit. Inside the gauge, a needle is deflected over a scale in proportion to the pressure within the conduit. In some instances, the standard pressure gauge may be replaced with a transducer, which converts pressure into an electrical signal, which is then monitored. One important medical application for a pressure sensor involves detecting a patient's blood pressure, and/or intracranial pressure.
- One typical method of monitoring blood pressure is to measure the fluid pressure within an intravenous tube, which is hydraulically coupled to the patient's vein. A catheter is inserted into the patient's vein and a plastic tube or conduit coupled to the catheter. A saline solution can be drip-fed through the plastic tubing or conduit to maintain a pressure balance against the pressure within the patient's vein. The saline fluid acts as a hydraulic fluid to cause the pressure within the plastic tubing to correspond to the pressure within the patient's vein. Hence, by measuring the fluid pressure within the tubing, the patient's blood pressure will be known.
- Various conventional SAW sensing devices are capable of measuring blood pressure. Such devices typically are configured from ceramic materials (like PZT), quartz-type piezoelectric materials or lithium niobate. Such devices are disadvantageous for medical applications, because the above-referenced materials utilized by such devices are inherently self-resonant, having extremely low piezoelectric coupling coefficient, expensive and difficult for micro-machining, and consequently, grossly reduce the possibility of making a low cost pressure sensor for medical applications.
- Conventional quartz-based SAW pressure sensors are also expensive to implement in medical applications, rendering their widespread use limited. Micro-machining in quartz is nothing close to that of silicon. It is therefore believed that a solution to such problems involves a disposable low cost sensor packaging system, particularly one that is suited to medical applications.
- The following summary is provided to facilitate an understanding of some of the innovative features unique to the embodiments disclosed herein and is not intended to be a full description. A full appreciation of the various aspects of the embodiments discussed herein can be gained by taking the entire specification, claims, drawings, and abstract as a whole.
- It is, therefore, one aspect of the present invention to provide for improved sensing devices and applications
- It is another aspect of the present invention to provide for improved pressure sensor devices, systems and methods thereof.
- It is a further aspect of the present invention to provide for an improved disposable wireless pressure sensor.
- It is an additional aspect of the present invention to provide for a pressure sensor system based on interdigital transducer (IDT) and polymer piezoelectric materials.
- The aforementioned aspects of the invention and other objectives and advantages can now be achieved as described herein. Disposable sensor systems and method are disclosed. In general, a dielectric polymer substrate provided and a microstrip antenna formed upon the dielectric polymer substrate. A piezoelectric polymer layer (e.g., a polyvinylidene fluoride (PVDF) piezoelectric film) and the microstrip antenna can be formed flexible in nature, which makes them suitable for conformal wraparound designs and applications. Additionally, an interdigital (IDT) layer can be configured upon the PVDF piezoelectric layer, thereby permitting the piezoelectric polymer layer and the IDT layer to detect pressure data and transmit the data to a receiver via the antenna.
- A first bonding layer can be formed between the dielectric polymer substrate and the piezoelectric polymer layer. Also, a second bonding layer can be formed between the IDT layer and the piezoelectric polymer layer. A protective cover layer can also be configured above the IDT layer. The IDT layer can be formed as a plurality of IDT finger electrodes, which may be configured from copper. Additionally, the polymer substrate can include a gap formed centrally therein, such that the gap is filled with a gel comprising a low thermal conductivity and bio-compatible material. The polymer substrate is generally formed from a low thermal conductivity dielectric substrate material.
- The accompanying figures, in which like reference numerals refer to identical or functionally-similar elements throughout the separate views and which are incorporated in and form a part of the specification, further illustrate the present invention and, together with the detailed description of the invention, serve to explain the principles of the present invention.
-
FIG. 1 illustrates a side view of a disposable wireless pressure sensor system, which can be implemented in accordance with a preferred embodiment; -
FIG. 2 illustrates a top view of the disposable wireless pressure sensor system depicted inFIG. 1 , in accordance with a preferred embodiment; -
FIG. 3 illustrates a schematic diagram of a medical pressure sensing system, which can be implemented in accordance with an alternative embodiment; and -
FIG. 4 illustrates a schematic diagram of a microstrip antenna, which can be implemented in accordance with a preferred embodiment. - The particular values and configurations discussed in these non-limiting examples can be varied and are cited merely to illustrate at least one embodiment of the present invention and are not intended to limit the scope of the invention.
-
FIG. 1 illustrates a side view of a disposable wirelesspressure sensor system 100, which can be implemented in accordance with a preferred embodiment.FIG. 2 illustrates a top view of the disposable wirelesspressure sensor system 100 depicted inFIG. 1 , in accordance with a preferred embodiment. Note that inFIGS. 1-2 , identical or similar parts are generally indicated by identical reference numerals.System 100 generally includes adielectric polymer substrate 102. - A
microstrip antenna 104 can be formed upon thedielectric polymer substrate 102. Additionally, apiezoelectric polymer layer 106 can be formed above the dielectric polymer substrate, while an interdigital (IDT)layer 108 can be configured upon thepiezoelectric polymer layer 106, thereby permitting thepiezoelectric polymer layer 106 and theIDT layer 108 to detect pressure data and transmit the data to a receiver utilizing theantenna 104. Thepiezoelectric polymer layer 106 can be configured as a thin sheet having a thickness in a range of 10-20 microns, depending upon design considerations. - Additionally, a
first bonding layer 114 can be formed between thedielectric polymer substrate 102 and thepiezoelectric polymer layer 106. Asecond bonding layer 112 can be formed between theIDT layer 108 and thepiezoelectric polymer layer 106. First and second bonding layers 114 and 112 function as adhesives. The adhesive material for bondinglayers layers - A
protective cover layer 110 can be formed above the IDT layer. Theprotective cover layer 110 can be formed as a protective plastic sheet in order to ensure mechanical and chemical protection ofsystem 100 as a whole. TheIDT layer 108 can be configured to includeIDT finger electrodes 116, which are depicted inFIG. 2 . Each of theIDT finger electrodes 116 can be formed from copper. The copper IDT thickness can be for example, in a range of approximately 25 micrometers to 125 micrometers, depending upon design considerations. Note that in order to provide lower frequency capabilities, a winder line width, along with bigger device sizes thereof, the IDT finger electrodes can be printed on thepiezoelectric polymer layer 106, or can be electroplated or etched form a large sheet of IDT finger electrodes thereof. - The
dielectric polymer substrate 102 can also be configured to include agap 120 filled with agel 122 formed from a low thermal conductivity and biocompatible material. Thepiezoelectric polymer layer 106 can be configured as a polyvinylidene fluoride (PVDF) piezoelectric film, while thedielectric polymer substrate 102 can be formed from a low thermal conductivity dielectric substrate material. It is believed that the use of PVDF piezoelectric film in accordance with the preferred embodiment described herein can result in substantial cost-savings and increased sensor efficiency, particularly in medical pressure sensing applications. - One example where
system 100 can be particularly useful is the field of medical applications, such as blood pressure sensing. The PVDF piezoelectric film is therefore formed on the biocompatible low thermal conductivitydielectric polymer substrate 102. The PVDF piezoelectric film changes with temperature and pressure. Utilizing a low thermal conductivity substrate, for example, the pyroelectric change by blood can be minimized. Theantenna 104 can be printed on the dielectric polymer substrate. Thus, in accordance with the preferred embodiment described herein, a number of transceivers can be provided including a piezoelectric polymer sheet material, which is less costly and much easier to work with than conventional pressure sensing devices. -
FIG. 3 illustrates a schematic diagram of a medicalpressure sensing system 300, which can be implemented in accordance with an alternative embodiment. Note that inFIGS. 1-3 , identical or similar parts or components are generally indicated by identical reference numerals. Thus, sensor orsystem 100 ofFIG. 1 is also depicted inFIG. 3 at a location relative to aconduit 301, which can be implemented as, for example, a catheter through which fluid 303 flow, as indicated byarrows Fluid 303 can be, for example, blood. System orsensor 100 can therefore transmit and receive data to and from a transmitter/receiver 304, which includes anantenna 306. The wireless transmission of such data is indicated inFIG. 3 byarrows 308.System 300 can therefore be utilized for measuring bodily fluid pressure withinconduit 301. -
FIG. 4 illustrates a schematic diagram of amicrostrip antenna 400, which can be implemented in accordance with a preferred embodiment.Microstrip antenna 400 generally includes adielectric substrate 404 located above aground plane 402. A radiatingpatch 406 is generally disposed on or insubstrate 404. Note thatmicrostrip antenna 400 ofFIG. 4 is analogous tomicrostrip antenna 104 ofFIG. 1 . For example,microstrip antenna 104 can be formed upon adielectric polymer substrate 102 as indicated inFIG. 1 . Thus,substrate 102 ofFIG. 1 is similar tosubstrate 404 ofFIG. 4 . - Because a dielectric polymer substrate, such as
substrate 404 can be flexible, the configuration ofmicrostrip antenna 400 is suitable for adaptation to conformal wrap-around type designs and applications. Microstrip antennas, such asantenna 400, offer a number of advantages compared to conventional microwave antennas such as, for example light weight, low volume, and thin profile configurations, which can be made conformal; low fabrication cost; and readily amendable to mass production. Linear and circular polarizations are also possible with simple feed configurations. Additionally, dual-frequency and dual-polarization antennas can be easily constructed; because, no cavity backing is required and such devices can be easily integrated with microwave circuits. - The embodiments and examples set forth herein are presented to best explain the present invention and its practical application and to thereby enable those skilled in the art to make and utilize the invention. Those skilled in the art, however, will recognize that the foregoing description and examples have been presented for the purpose of illustration and example only. Other variations and modifications of the present invention will be apparent to those of skill in the art, and it is the intent of the appended claims that such variations and modifications be covered.
- The description as set forth is not intended to be exhaustive or to limit the scope of the invention. Many modifications and variations are possible in light of the above teaching without departing from the scope of the following claims. It is contemplated that the use of the present invention can involve components having different characteristics. It is intended that the scope of the present invention be defined by the claims appended hereto, giving full cognizance to equivalents in all respects.
Claims (20)
1. A disposable sensor system, comprising:
a dielectric polymer substrate and an antenna formed upon said dielectric polymer substrate;
a piezoelectric polymer layer formed above said dielectric polymer substrate; and
an interdigital (IDT) layer formed upon said piezoelectric polymer layer, thereby permitting said piezoelectric polymer layer and said IDT layer to detect pressure data and transmit said data to a receiver utilizing said antenna.
2. The system of claim 1 further comprising:
a bonding layer formed between said dielectric polymer substrate and said piezoelectric polymer layer.
3. The system of claim 1 further comprising:
a bonding layer formed between said IDT layer and said piezoelectric polymer layer.
4. The system of claim 1 further comprising a protective cover layer formed above said IDT layer.
5. The system of claim 1 wherein said IDT layer comprises a plurality of IDT finger electrodes.
6. The system of claim 5 wherein each of said IDT finger electrodes among said plurality of IDT finger electrodes comprise copper.
7. The system of claim 1 wherein said dielectric polymer substrate comprises a gap formed centrally therein, wherein said gap is filled with a gel comprising a low thermal conductivity and biocompatible material.
8. The system of claim 1 wherein said piezoelectric polymer layer comprises a polyvinylidene fluoride (PVDF) piezoelectric film.
9. The system of claim 1 wherein said dielectric polymer substrate comprises a low thermal conductivity dielectric substrate material.
10. The system of claim 1 wherein said antenna is printed on said dielectric polymer substrate.
11. A disposable sensor system, comprising:
a dielectric polymer substrate and an antenna formed upon said dielectric polymer substrate, wherein said dielectric polymer substrate comprises a low thermal conductivity dielectric substrate material;
a piezoelectric polymer layer formed above said dielectric polymer substrate, said dielectric polymer substrate comprises a gap formed centrally therein, wherein said gap is filled with a gel comprising a low thermal conductivity and bio-compatible material and wherein said piezoelectric polymer layer comprises a polyvinylidene fluoride (PVDF) piezoelectric film;
an interdigital (IDT) layer formed upon said piezoelectric polymer layer, wherein said IDT layer comprises a plurality of IDT finger electrodes;
a protective cover layer formed above said IDT layer;
a first bonding layer formed between said dielectric polymer substrate and said piezoelectric polymer layer; and
a second bonding layer formed between said IDT layer and said piezoelectric polymer layer, thereby permitting said piezoelectric polymer layer and said IDT layer to detect pressure data and transmit said data to a receiver utilizing said antenna.
12. A disposable sensor method, comprising the steps:
forming an antenna upon a dielectric polymer substrate;
configuring a piezoelectric polymer layer above said dielectric polymer substrate; and
locating an interdigital (IDT) layer upon said piezoelectric polymer layer, thereby permitting said piezoelectric polymer layer and said IDT layer to detect pressure data and transmit said data to a receiver utilizing said antenna.
13. The method of claim 12 further comprising the step of forming a bonding layer between said dielectric polymer substrate and said piezoelectric polymer layer.
14. The method of claim 12 further comprising the step of forming a bonding layer between said IDT layer and said piezoelectric polymer layer.
15. The method of claim 12 further comprising the step of forming a protective cover layer above said IDT layer.
16. The method of claim 12 further comprising the step of configuring said IDT layer to comprise a plurality of IDT finger electrodes comprising copper.
17. The method of claim 12 further comprising the steps of:
forming a gap from centrally form said dielectric polymer substrate; and
filling said gap with a gel comprising a low thermal conductivity and biocompatible material.
18. The method of claim 12 further comprising the step of configuring said piezoelectric polymer layer as a polyvinylidene fluoride (PVDF) piezoelectric film.
19. The method of claim 12 further comprising the step of configuring said dielectric polymer substrate from a low thermal conductivity dielectric substrate material.
20. The method of claim 12 wherein the step of forming said antenna upon said dielectric polymer substrate further comprises the step of printing said antenna on said dielectric polymer substrate.
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/995,460 US7059196B1 (en) | 2004-11-22 | 2004-11-22 | Disposable wireless pressure sensor |
EP05824813A EP1815222A1 (en) | 2004-11-22 | 2005-11-21 | Disposable wireless pressure sensor with interdigital layer formed upon a piezoelectric polymer layer |
CNA2005800468472A CN101115982A (en) | 2004-11-22 | 2005-11-21 | Disposable wireless pressure sensor with interdigital layer formed upon a piezoelectric polymer layer |
PCT/US2005/042255 WO2006057987A1 (en) | 2004-11-22 | 2005-11-21 | Disposable wireless pressure sensor with interdigital layer formed upon a piezoelectric polymer layer |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/995,460 US7059196B1 (en) | 2004-11-22 | 2004-11-22 | Disposable wireless pressure sensor |
Publications (2)
Publication Number | Publication Date |
---|---|
US20060107749A1 true US20060107749A1 (en) | 2006-05-25 |
US7059196B1 US7059196B1 (en) | 2006-06-13 |
Family
ID=35811410
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/995,460 Expired - Fee Related US7059196B1 (en) | 2004-11-22 | 2004-11-22 | Disposable wireless pressure sensor |
Country Status (4)
Country | Link |
---|---|
US (1) | US7059196B1 (en) |
EP (1) | EP1815222A1 (en) |
CN (1) | CN101115982A (en) |
WO (1) | WO2006057987A1 (en) |
Cited By (15)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20090007679A1 (en) * | 2007-07-03 | 2009-01-08 | Endotronix, Inc. | Wireless pressure sensor and method for fabricating wireless pressure sensor for integration with an implantable device |
US20090036754A1 (en) * | 2007-07-31 | 2009-02-05 | Captomed Eurl | Self-calibrating pressure sensor |
US20100022894A1 (en) * | 2008-07-28 | 2010-01-28 | Biotronik Vi Patent Ag | Intravascular Measurement |
US7901360B1 (en) * | 2007-05-17 | 2011-03-08 | Pacesetter, Inc. | Implantable sensor for measuring physiologic information |
US20110137184A1 (en) * | 2008-08-19 | 2011-06-09 | Fan Ren | Pressure sensing |
US20130150225A1 (en) * | 2011-12-07 | 2013-06-13 | Fenwal, Inc. | Pressure sensor |
US20160247999A1 (en) * | 2015-02-23 | 2016-08-25 | Commissariat à I'énergie atomique et aux énergies alternatives | Piezoelectric device |
CN106441073A (en) * | 2016-09-05 | 2017-02-22 | 西安交通大学 | Dielectric flexible sensor for big deformation and touch pressure measurement |
US10430624B2 (en) | 2017-02-24 | 2019-10-01 | Endotronix, Inc. | Wireless sensor reader assembly |
WO2022098335A3 (en) * | 2020-11-03 | 2022-06-09 | Koc Universitesi | An intracranial pressure sensor |
US11615257B2 (en) | 2017-02-24 | 2023-03-28 | Endotronix, Inc. | Method for communicating with implant devices |
US11666239B2 (en) | 2017-03-14 | 2023-06-06 | University Of Connecticut | Biodegradable pressure sensor |
US11678989B2 (en) * | 2019-03-01 | 2023-06-20 | University Of Connecticut | Biodegradable piezoelectric nanofiber scaffold for bone or tissue regeneration |
US11745001B2 (en) | 2020-03-10 | 2023-09-05 | University Of Connecticut | Therapeutic bandage |
US11826495B2 (en) | 2019-03-01 | 2023-11-28 | University Of Connecticut | Biodegradable piezoelectric ultrasonic transducer system |
Families Citing this family (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
ES2299392B1 (en) | 2006-11-14 | 2009-04-16 | Consejo Superior Investigaciones Cientificas | ORGANIC SENSOR DEVICE AND ITS APPLICATIONS. |
DE602007008291D1 (en) * | 2007-01-04 | 2010-09-16 | Sense As | SYSTEM FOR MEASURING BLOOD PRESSURE IN AN ARTERY |
CN100453989C (en) * | 2007-06-19 | 2009-01-21 | 杭州电子科技大学 | Array piezoelectric sensor |
FR2925696B1 (en) | 2007-12-21 | 2011-05-06 | Senseor | SURFACE WAVE PASSIVE SENSOR COMPRISING AN INTEGRATED ANTENNA AND MEDICAL APPLICATIONS USING THIS TYPE OF PASSIVE SENSOR |
DE102008011682A1 (en) * | 2008-02-28 | 2009-09-03 | Robert Bosch Gmbh | Pressure distribution measuring device for component surface in ultrasound supported cleaning bath, has converter material connected with base and counter electrodes, where electrodes combined forms sensor element |
US20100114063A1 (en) * | 2008-11-04 | 2010-05-06 | Angiodynamics, Inc. | Catheter injection monitoring device |
DE102011081887A1 (en) * | 2011-08-31 | 2013-02-28 | Robert Bosch Gmbh | Polymer layer system pressure sensor device and polymer layer system pressure sensor method |
RU2020132467A (en) | 2018-03-05 | 2022-04-05 | Юниверсити Оф Коннектикут | MICRONEEDLE PLATFORM WITH CORE-SHELL STRUCTURE FOR TRANSDERMAL AND PULSATING DRUG/VACCINE DELIVERY AND METHOD FOR ITS MANUFACTURE |
Citations (16)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3931446A (en) * | 1970-09-26 | 1976-01-06 | Kureha Kagaku Kogyo Kabushiki Kaisha | Process for producing polymeric piezoelectric elements and the article formed thereby |
US4600855A (en) * | 1983-09-28 | 1986-07-15 | Medex, Inc. | Piezoelectric apparatus for measuring bodily fluid pressure within a conduit |
US5675314A (en) * | 1996-02-09 | 1997-10-07 | The University Of British Columbia | Tire pressure sensor |
US5821425A (en) * | 1996-09-30 | 1998-10-13 | The United States Of America As Represented By The Secretary Of The Army | Remote sensing of structural integrity using a surface acoustic wave sensor |
US6144288A (en) * | 1997-03-28 | 2000-11-07 | Eaton Corporation | Remote wireless switch sensing circuit using RF transceiver in combination with a SAW chirp processor |
US6293136B1 (en) * | 1999-08-26 | 2001-09-25 | The United States Of America As Represented By The Secretary Of The Army | Multiple mode operated surface acoustic wave sensor for temperature compensation |
US6301973B1 (en) * | 1999-04-30 | 2001-10-16 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Non-intrusive pressure/multipurpose sensor and method |
US6475170B1 (en) * | 1997-12-30 | 2002-11-05 | Remon Medical Technologies Ltd | Acoustic biosensor for monitoring physiological conditions in a body implantation site |
US6486588B2 (en) * | 1997-12-30 | 2002-11-26 | Remon Medical Technologies Ltd | Acoustic biosensor for monitoring physiological conditions in a body implantation site |
US6504286B1 (en) * | 1997-12-30 | 2003-01-07 | Remon Medical Technologies Ltd. | Piezoelectric transducer |
US20030107454A1 (en) * | 2001-10-29 | 2003-06-12 | Hiroyuki Nakamura | Surface acoustic wave filter element, surface acoustic wave filter and communication device using the same |
US6640613B2 (en) * | 1999-10-15 | 2003-11-04 | Forschungszentrum Karlsruhe Gmbh | Method for producing surface acoustic wave sensors and such a surface acoustic wave sensor |
US6670739B2 (en) * | 2001-03-02 | 2003-12-30 | Murata Manufacturing Co., Ltd. | Surface acoustic wave apparatus |
US6681623B2 (en) * | 2001-10-30 | 2004-01-27 | Honeywell International Inc. | Flow and pressure sensor for harsh fluids |
US6953977B2 (en) * | 2000-02-08 | 2005-10-11 | Boston Microsystems, Inc. | Micromechanical piezoelectric device |
US20050225200A1 (en) * | 2004-04-05 | 2005-10-13 | Honeywell International, Inc. | Passive wireless piezoelectric smart tire sensor with reduced size |
Family Cites Families (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5212988A (en) * | 1988-02-29 | 1993-05-25 | The Reagents Of The University Of California | Plate-mode ultrasonic structure including a gel |
WO2002076289A2 (en) * | 2001-03-27 | 2002-10-03 | Kain Aron Z | Wireless system for measuring distension in flexible tubes |
-
2004
- 2004-11-22 US US10/995,460 patent/US7059196B1/en not_active Expired - Fee Related
-
2005
- 2005-11-21 CN CNA2005800468472A patent/CN101115982A/en active Pending
- 2005-11-21 WO PCT/US2005/042255 patent/WO2006057987A1/en active Application Filing
- 2005-11-21 EP EP05824813A patent/EP1815222A1/en not_active Withdrawn
Patent Citations (17)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3931446A (en) * | 1970-09-26 | 1976-01-06 | Kureha Kagaku Kogyo Kabushiki Kaisha | Process for producing polymeric piezoelectric elements and the article formed thereby |
US4600855A (en) * | 1983-09-28 | 1986-07-15 | Medex, Inc. | Piezoelectric apparatus for measuring bodily fluid pressure within a conduit |
US5675314A (en) * | 1996-02-09 | 1997-10-07 | The University Of British Columbia | Tire pressure sensor |
US5821425A (en) * | 1996-09-30 | 1998-10-13 | The United States Of America As Represented By The Secretary Of The Army | Remote sensing of structural integrity using a surface acoustic wave sensor |
US6144288A (en) * | 1997-03-28 | 2000-11-07 | Eaton Corporation | Remote wireless switch sensing circuit using RF transceiver in combination with a SAW chirp processor |
US6486588B2 (en) * | 1997-12-30 | 2002-11-26 | Remon Medical Technologies Ltd | Acoustic biosensor for monitoring physiological conditions in a body implantation site |
US6475170B1 (en) * | 1997-12-30 | 2002-11-05 | Remon Medical Technologies Ltd | Acoustic biosensor for monitoring physiological conditions in a body implantation site |
US6504286B1 (en) * | 1997-12-30 | 2003-01-07 | Remon Medical Technologies Ltd. | Piezoelectric transducer |
US6301973B1 (en) * | 1999-04-30 | 2001-10-16 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Non-intrusive pressure/multipurpose sensor and method |
US6293136B1 (en) * | 1999-08-26 | 2001-09-25 | The United States Of America As Represented By The Secretary Of The Army | Multiple mode operated surface acoustic wave sensor for temperature compensation |
US6640613B2 (en) * | 1999-10-15 | 2003-11-04 | Forschungszentrum Karlsruhe Gmbh | Method for producing surface acoustic wave sensors and such a surface acoustic wave sensor |
US6953977B2 (en) * | 2000-02-08 | 2005-10-11 | Boston Microsystems, Inc. | Micromechanical piezoelectric device |
US6670739B2 (en) * | 2001-03-02 | 2003-12-30 | Murata Manufacturing Co., Ltd. | Surface acoustic wave apparatus |
US20030107454A1 (en) * | 2001-10-29 | 2003-06-12 | Hiroyuki Nakamura | Surface acoustic wave filter element, surface acoustic wave filter and communication device using the same |
US6681623B2 (en) * | 2001-10-30 | 2004-01-27 | Honeywell International Inc. | Flow and pressure sensor for harsh fluids |
US20050225200A1 (en) * | 2004-04-05 | 2005-10-13 | Honeywell International, Inc. | Passive wireless piezoelectric smart tire sensor with reduced size |
US6958565B1 (en) * | 2004-04-05 | 2005-10-25 | Honeywell International Inc. | Passive wireless piezoelectric smart tire sensor with reduced size |
Cited By (26)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8257272B2 (en) | 2007-05-17 | 2012-09-04 | Pacesetter, Inc. | Implantable sensor for measuring physiologic information |
US20110137187A1 (en) * | 2007-05-17 | 2011-06-09 | Pacesetter, Inc. | Implantable sensor for measuring physiologic information |
US7901360B1 (en) * | 2007-05-17 | 2011-03-08 | Pacesetter, Inc. | Implantable sensor for measuring physiologic information |
US7677107B2 (en) | 2007-07-03 | 2010-03-16 | Endotronix, Inc. | Wireless pressure sensor and method for fabricating wireless pressure sensor for integration with an implantable device |
US20090007679A1 (en) * | 2007-07-03 | 2009-01-08 | Endotronix, Inc. | Wireless pressure sensor and method for fabricating wireless pressure sensor for integration with an implantable device |
US8622923B2 (en) | 2007-07-31 | 2014-01-07 | Captomed Eurl | Self-calibrating pressure sensor |
EP2022395A1 (en) * | 2007-07-31 | 2009-02-11 | Captomed EURL | Self-calibrating pressure sensor |
FR2919486A1 (en) * | 2007-07-31 | 2009-02-06 | Captomed Entpr Unipersonnelle | SELF-CALIBRAL PRESSURE SENSOR. |
US20090036754A1 (en) * | 2007-07-31 | 2009-02-05 | Captomed Eurl | Self-calibrating pressure sensor |
DE102008040790A1 (en) * | 2008-07-28 | 2010-02-04 | Biotronik Vi Patent Ag | Intravascular measurement of flow mechanical parameters by means of SAW transponder |
US20100022894A1 (en) * | 2008-07-28 | 2010-01-28 | Biotronik Vi Patent Ag | Intravascular Measurement |
US20110137184A1 (en) * | 2008-08-19 | 2011-06-09 | Fan Ren | Pressure sensing |
US20130150225A1 (en) * | 2011-12-07 | 2013-06-13 | Fenwal, Inc. | Pressure sensor |
US9404825B2 (en) * | 2011-12-07 | 2016-08-02 | Fenwal, Inc. | Apparatus with flexible member for sensing fluid pressure |
US10188784B2 (en) | 2011-12-07 | 2019-01-29 | Fenwal, Inc. | Apparatus with rigid member for sensing fluid pressure |
US10090455B2 (en) * | 2015-02-23 | 2018-10-02 | Commissariat à l'énergie atomique et aux énergies alternatives | Piezoelectric device |
US20160247999A1 (en) * | 2015-02-23 | 2016-08-25 | Commissariat à I'énergie atomique et aux énergies alternatives | Piezoelectric device |
CN106441073A (en) * | 2016-09-05 | 2017-02-22 | 西安交通大学 | Dielectric flexible sensor for big deformation and touch pressure measurement |
US10430624B2 (en) | 2017-02-24 | 2019-10-01 | Endotronix, Inc. | Wireless sensor reader assembly |
US11461568B2 (en) | 2017-02-24 | 2022-10-04 | Endotronix, Inc. | Wireless sensor reader assembly |
US11615257B2 (en) | 2017-02-24 | 2023-03-28 | Endotronix, Inc. | Method for communicating with implant devices |
US11666239B2 (en) | 2017-03-14 | 2023-06-06 | University Of Connecticut | Biodegradable pressure sensor |
US11678989B2 (en) * | 2019-03-01 | 2023-06-20 | University Of Connecticut | Biodegradable piezoelectric nanofiber scaffold for bone or tissue regeneration |
US11826495B2 (en) | 2019-03-01 | 2023-11-28 | University Of Connecticut | Biodegradable piezoelectric ultrasonic transducer system |
US11745001B2 (en) | 2020-03-10 | 2023-09-05 | University Of Connecticut | Therapeutic bandage |
WO2022098335A3 (en) * | 2020-11-03 | 2022-06-09 | Koc Universitesi | An intracranial pressure sensor |
Also Published As
Publication number | Publication date |
---|---|
CN101115982A (en) | 2008-01-30 |
WO2006057987A1 (en) | 2006-06-01 |
EP1815222A1 (en) | 2007-08-08 |
US7059196B1 (en) | 2006-06-13 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7059196B1 (en) | Disposable wireless pressure sensor | |
US7017416B1 (en) | Disposable pressure diaphragm and wireless sensor systems and methods | |
US7290454B2 (en) | Pressure flow sensor systems and pressure flow sensors for use therein | |
US7146861B1 (en) | Disposable and trimmable wireless pressure sensor | |
US7059195B1 (en) | Disposable and trimmable wireless pressure sensor for medical applications | |
US7694570B1 (en) | Non-invasive dry coupled disposable/reusable ultrasonic sensor | |
US4600855A (en) | Piezoelectric apparatus for measuring bodily fluid pressure within a conduit | |
US5798462A (en) | Magnetic position sensor with magnetic field shield diaphragm | |
US7331236B2 (en) | Pressure sensor | |
JP4621257B2 (en) | Variable inductor type MEMS pressure sensor using magnetostrictive effect | |
US7825568B2 (en) | Electro acoustic sensor for high pressure environments | |
EP1837638B1 (en) | Pressure sensor | |
JP5138246B2 (en) | Pressure sensor | |
CN102575954B (en) | For measuring the sensing system of fluid velocity | |
WO1989001311A1 (en) | Tubular pressure transducer | |
US11841251B2 (en) | Direct implementation of sensors in tubes | |
WO2006030405A1 (en) | A transducer apparatus for measuring biomedical pressures | |
US8770010B1 (en) | Integrated detector for detecting bubbles in fluid flow and occlusions in a tube | |
Park et al. | Hermetically sealed inductor-capacitor (LC) resonator for remote pressure monitoring | |
WO2012079091A2 (en) | Self-heated mems based capacitance diaphragm gauge | |
JPS60220833A (en) | Surface wave sensor | |
KR100924417B1 (en) | Electro acoustic sensor for high pressure environment | |
CN110160439B (en) | Contact type flexible sensor | |
WO2023144823A1 (en) | Surface/tactile sensor configurations and applications thereof | |
Payne et al. | Polymer materials for pressure measurement |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: HONEYWELL INTERNATIONAL, INC., NEW JERSEY Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:LIU, JAMES Z.;COOK, JAMES D.;DIERAUER, PETER F.;REEL/FRAME:016030/0813 Effective date: 20041122 |
|
REMI | Maintenance fee reminder mailed | ||
LAPS | Lapse for failure to pay maintenance fees | ||
STCH | Information on status: patent discontinuation |
Free format text: PATENT EXPIRED DUE TO NONPAYMENT OF MAINTENANCE FEES UNDER 37 CFR 1.362 |
|
FP | Expired due to failure to pay maintenance fee |
Effective date: 20100613 |