Patent Document

ORIGIN OF THE INVENTION 
     The invention described herein was made by employees of the United States Government and may be manufactured and used by or for the Government, for Government purposes, without the payment of any royalties thereon or therefore. 
    
    
     BACKGROUND OF THE INVENTION 
     1. Field of the Invention 
     The present invention generally relates to combining Radio Frequency (RF) technology with novel micro-inductor antennas and signal processing circuits for RF telemetry of real time, measured data, from microelectromechanical system (MEMS) sensors, through electromagnetic coupling with a remote powering/receiving device. Such technology has many applications, but is especially useful in the biomedical area. 
     2. Description of the Prior Art 
     The prior art teaches capacitive sensors and switches that may be embedded within apparatus to perform remote sensing functions. However, the devices of the prior art are relatively complicated in structure and require the presence of a directly coupled power source. For example see the following U.S. Pat. Nos. 3,852,755; 4,857,893; 5,300,875; 5,335,361; 5,440,300; 5,461,385; 5,621,913; and 5,970,393. 
     BRIEF SUMMARY OF THE INVENTION 
     The present invention teaches a microminiaturized inductor/antenna system for contact-less powering of an oscillator circuit providing an RF telemetry signal from biomicroelectromechanical (bio-MEMS) systems, sensors, and/or actuators. A miniaturized circuit inductor coil is printed on a dielectric substrate. The inductor coil behaves both as an inductor, which acts to charge a capacitive device as well as an antenna for transmitting a RF signal indicative of the level of charge of the capacitive device. 
     The micro-miniature circuit operates in two modes. In the first mode, the inductance coil forms a series resonant circuit with the capacitance of a capacitive MEMS device such as a pressure-sensing diaphragm of a MEMS pressure sensor device. In the second mode, the capacitive device produces an oscillating electrical current flow through a planar printed inductor coil. The inductor coil is equivalent to a helical antenna and hence loses power through RF radiation from the inductor. A remote RF receiving device may be used to receive the RF radiation, from the inductor coil, as a RF telemetry signal. The functional operation begins when an electromagnetic coupling energizes the circuit with a remote-transmitting device followed by oscillation of the circuit. Thus there is no direct or hard connection to the circuit by any power source. 
    
    
     BRIEF DESCRIPTION OF THE DRAWINGS 
     FIG. 1 presents a schematic diagram of the electrical oscillator circuit embodied in the present invention. 
     FIG. 2 presents a curve showing the amplitude and frequency, as a function of time, for the oscillating signal produced by the oscillator circuit illustrated in FIG.  1 . 
     FIG. 2A presents a plot of measured resonance frequency vs. chip capacitor values for an oscillating circuit having a 150 nH inductor. 
     FIG. 3 presents a similar electrical circuit as shown in FIG. 1 having a microelectronic capacitive sensor device therein. 
     FIG. 4 presents a, greatly enlarged, schematical illustration of a pressure sensing/transmitting MEMS microchip embodying the present invention. 
     FIG. 4A presents an elevational crossection taken along line  4 A— 4 A in FIG. 4 having a single micro capacitive pressure sensor. 
     FIG. 5 presents a graphical plot of capacitance vs. pressure for a typical microelectronic capacitive pressure sensor. 
     FIG. 6 presents a schematical elevational view, similar to that of FIG. 5 showing an alternate embodiment of the present invention having dual micro capacitive pressure sensors. 
     FIG. 6A presents an electrical schematic of the circuit diagram for the FIG. 6 embodiment. 
     FIG. 7 is a plan view taken along line  7 — 7  in FIG. 5 showing a continuous ring type electrical ground plane. 
     FIG. 8 presents a greatly enlarged view of a square, planar, inductor coil suitable for use with the present invention. 
     FIG. 9 presents a representative plot of pressure and strain vs. time for a spinal implant typically used in spinal surgery. 
     FIG. 10 presents a planar view, similar to that of FIG. 7 showing an alternative ground plane configuration suitable for use with the present invention. 
    
    
     DETAILED DESCRIPTION OF THE INVENTION 
     FIG. 1 illustrates a simple oscillator circuit  10  comprising an inductor coil  12  and a capacitor  14 . If inductor  12  is subjected to a magnetic field  18  from a remote electromagnetic source  15 , an electrical current is created within inductor  12 , which will flow to and charge capacitor  14 . Upon capacitor  14  becoming fully charged, current flow from induction coil  12  will stop. When the magnetic field  18  is removed, current will flow from capacitor  14  energizing inductor  12 . Upon capacitor  14  transferring all of its energy, minus losses, to inductor  12 , the electromagnetic energy now stored within inductor  12  will once again flow back to capacitor  14  thereby recharging capacitor  12 . This “oscillating” process will continue until the total electromagnetic energy within circuit  10  dissipates. During this oscillation, inductor  12  will radiate RF energy  16  at a frequency determined by the properties of capacitor  14  and inductor  12 . 
     FIG. 2 illustrates the RF signal transmitted from inductor  12 , as a function of time t, after the magnetic field  18  has been removed. As illustrated in FIG. 2, the amplitude A of the RF signal decays as a function of time t, however, the frequency f of the signal remains constant. 
     FIG. 2A presents a plot of the measured RF signal frequency as a function of capacitor values for an oscillating circuit having a 150 nH inductor coil. 
     Referring now to FIG. 3, a similar circuit  20 , as that shown in FIG. 1, is illustrated wherein the capacitor  14  has been replaced with a “microelectromechanical (MEMS) capacitive sensing device  24  such as a MEMS pressure sensing device. MEMS pressure sensing device  24  may be placed at a pressure sensing location where real time pressure measurement is desired. When a pressure measurement is desired to be taken, a remote magnetic field  18 , from electromagnetic source  15 , is used to energize inductor  12  which causes an electrical current to flow from inductor  12  to MEMS pressure sensor  24 . Pressure sensor  24  will thus be charged to the limit of its capacitance which is a function of the pressure that sensor  24  is measuring at that time. 
     Thus circuit  20 , illustrated in FIG. 3, represents a “contact less” MEMS pressure measuring system, requiring no directly connected power source such as a battery etc. Circuit  20 , is energized by a remotely generated magnetic field  18  from electromagnetic source  15 , acting through inductor  12 , thereby charging capacitive sensor  24  to an electrical energy state commensurate with the real time pressure being measured by sensor  24 . 
     Circuit  20  has many MEMS applications where a continuous pressure read-out is not necessarily required but where a periodic check of real time pressure is desired. Such an application may be particularly useful in in-vivo medical applications. 
     FIG. 4 presents a, greatly enlarged, schematic illustration of a MEMS capacitive pressure sensing device  36  in accord with the present invention. A suitable substrate material  32 , such as silicon, has MEMS capacitive pressure sensor circuit  30  attached thereto. Encircling MEMS pressure sensor  42  is a planar micro-inductor coil  34 . Additionally any other desired solid state circuits including microprocessor  39  might be added to the chip and linked to circuit  30 . 
     Thus when a real time, instantaneous, pressure measurement is desired, an electromagnetic field may be directed toward inductor coil  34 . Inductor coil  34  will charge capacitive pressure sensor  42  to an electrical energy level commensurate with the capacitance of sensor  42  at the time inductor coil  34  is energized. Upon removal of the electromagnetic field from inductor coil  34 , the electrical energy stored within MEMS pressure sensor  42  will now energize inductor coil  34 . The oscillator circuit formed by inductor coil  34  and capacitive pressure sensor MEMS  42  will now radiate a measurable RF signal proportionate to the capacitive value of MEMS pressure sensor  42 . 
     Typical overall dimensions of the inductor/antenna coil  34  encircling the MEMS pressure sensor  42  and the solid state circuits  39  may be as small as 1 mm×1 mm. Substrate  32  may be a high resistivity silicon that will reduce the attenuation of the RF signal radiated from the inductor coil. Metalization of inductor coil  34  may be chrome/gold approximately 150 Angstroms and 2 microns thick respectively. 
     Although FIG. 4 illustrates one and one half loops for coil  34 , a more typical embodiment would comprise ten or more loops as illustrated in FIG.  8 . The number of inductor coil loops will be dependent upon the range of capacitance values selected for MEMS pressure sensor  42  and the desired RF transmittal frequency of the installation. 
     Inductor coil  34  serves both as an inductor and as an antenna whereby coil  34  may operate in two modes. In the first mode, or charging mode, inductor coil  34  forms a series resonant oscillator circuit with the pressure measuring diaphragm of MEMS pressure sensor  42 , whereby the capacitance of MEMS pressure sensor  42  will change in proportion to the pressure being applied to its pressure sensitive diaphragm. 
     In the second mode, or transmitting mode, inductor coil  34  serves as an antenna and radiates measurable RF energy at a frequency determined by the capacitance level of MEMS pressure sensor  42 . FIG. 5 presents a representative plot of capacitance vs. pressure for a typical MEMS capacitive pressure sensor. 
     FIG. 8 illustrates a planar, inductor coil  50  suitable for use in pressure sensor circuit  30 . Inductor coil  50  comprises 10 turns each turn having a strip width of 15 microns and a gap width of 10 microns. The overall size of coil  50  approximates a 1,000 micron square. 
     Referring to FIGS. 4 and 5, the preferred embodiment of the present invention will be described. MEMS pressure sensor  42  is formed upon a high resistivity silicon wafer  32  by etching cavity  40  out of wafer  32  as illustrated in FIG. 5. A “Spin-On-Glass” (SOG) coating  38  is applied to the top surface of silicon chip  32 , upon which a first, rigid, capacitor plate  25  and planar inductor coil  34  are applied thereon, carefully positioning capacitor plate  25  directly over cavity  40 . A second, suitable membrane  56  comprising a tri-layer of SiO 2 /Si3N 3 /SiO 2  700 Å/3000 Å/4000 Å is applied over the bottom of wafer  32  having a second, pliable, pressure sensing capacitor plate  44  thereon. Capacitor plate  44  is carefully positioned opposite plate  42  and extends over cavity  40  as illustrated in FIG.  5 . Parallel plates  25  and  44  cooperate to form a microminiature capacitor with capacitor plate  44  exposed to the pressure being measured. As pressure is applied to plate  44 , plate  44  will necessarily yield in proportion to the applied pressure as indicated by arrow  43 . As the distance between plate  25  and  44  changes, the capacitance of the microminiature capacitor will also, proportionately, change. See FIG. 5 for a representative plot of capacitance vs. measured pressure for typical MEMS pressure sensors. 
     The capacitor formed by plates  25  and  44  coupled with inductor coil  34  forms a micro miniature oscillating circuit similar to that described in FIG. 3. A planar electrical ground plane  58  may be added to the chip structure and coupled to inductor/antenna  34 . For example a full ground plane may be used or a ring type ground plane illustrated in FIG.  7 . Alternatively a serrated ground plane  59  as illustrated in FIG. 10 may be replace the ring type ground plane as illustrated in FIG.  7 . 
     Table 6 presents measured quality factors (Q) for a planar inductor having a, full ground plane, a ring shaped ground plane, a serrated-ring shaped ground plane, and with no ground plane. It is seen from the data in Table 6 that a serrated ring ground plane out performs the other ground plane configurations. 
     Insulating layer  38  isolates the printed circuit from the substrate losses. Typically, the thickness of insulating layer  38  will be approximately 1 to 2 microns. Following application of insulating layer  38  the wafer  32  is patterned using photo resist and the inductor coil  34  is fabricated thereon using standard “lift-off” techniques. A suitable inductor coil thickness should lie within the range of 1.5 to 2.25 microns to minimize resistive losses in the circuit. 
     MEMS pressure sensors typically measure as little as 0.350 mm in width making them small enough for use in many in-vivo medical applications. For example, with one implanted MEMS pressure sensor it is possible to measure the internal pressure of body organs or wounds. With two MEMS pressure sensors it is possible to measure the pressure drop across an obstruction in an artery or newly implanted heart valve. With three MEMS sensors it is possible to characterize the flow across a long section of arteries, along the esophagus or through the small intestines. 
     FIG. 6 presents a schematical crossection, similar to that of FIG. 4, wherein a second silicon wafer  46  is applied atop wafer  32  sandwiching fixed capacitor plate  42  and planar inductor coil  34  therebetween as illustrated. A second cavity  50 , similar to cavity  40 , is etched into wafer  46  and positioned opposite cavity  40 . A second membrane  55 , including a flexible micro-miniature capacitor plate  48 , similar to capacitor plate  44 , is applied to the exposed surface of wafer  46  positioning capacitor plate  48  opposite capacitor plate  42 . Capacitor plate  44  is exposed to a first pressure source P 1  and capacitor plate  48  is exposed to a second pressure source P 2 . As capacitor plate  48  is exposed to varying pressure, capacitor plate  48  will yield in proportion to the pressure being applied thereto, as indicated by arrow  53  thereby varying the capacitance C 2  between plate  42  and  48 . 
     Where a pressure differential is the desired end product, capacitance values C 1  and C 2  may be read and compared (C 1 -C 2 ) by a micro-integrating circuit  54  (see FIG.  6 A). Integrating circuit  54  in combination with inductor coil  34  [(C 1 -C 2 )L] would then transmit an RF signal representing the differential pressure as measured by dual pressure measuring MEMS chip  52 . 
     FIG. 6A presents the equivalent electrical circuit for the dual MEMS pressure sensors illustrated in FIG.  6 . Integrator  54  measures the values of C 1  (between capacitor plates  42  and  44 ) and C 2  (between capacitor plates  42  and  48 ) and upon determining the difference therebetween establishes an oscillating circuit with inductor coil  34  whereby an RF signal is transmitted representing the pressure differential between P 1  and P 2 . 
     Such a dual pressure measuring MEMS may find use in any number of applications. For example such a differential pressure measuring MEMS may particularly find use in measuring the pressure differential between the upper cambered surface and the lower non-cambered surface of a relatively thin experimental airfoil test section in a wind tunnel thereby eliminating the need to accommodate cumbersome wiring and/or tubing which otherwise may not be accommodated within such a test environment. A second example is a submersible, underwater transport vehicle for maintaining the structural integrity of the vehicle. A third example is a pressure vessel for a chemical processing plant. Similarly a multiplicity of single MEMS pressure sensors might be used. 
     A parametric study has been conducted to investigate the effect on quality factor (Q), of the above described micro-circuits, by varying the width and separation between inductor coils; thickness of the SOG layer separating the inductor coils from the “High Resistivity Silicon” (HRSi) wafer; and the presence of a continuous, ring shaped, or serrated, ground plane. 
     Fabrication of the test chips comprised coating a high resistivity silicon wafer  32  with a thin insulating layer of SOG  38  to isolate the printed circuit from substrate losses. Typically the thickness of the insulating SOG layer  38  was about 1 to 2 microns. Following application of the SOG layer  38 , the wafer was patterned using photo resist and the inductor coils were fabricated using standard “lift-off techniques. Inductor thickness was in the range of 1.5 to 2.25 microns to minimize resistive losses in the circuit. FIG. 8 illustrates a typical micro inductor/antenna circuit having ten square loop turns as used in the herein reported tests. 
     In conducting the parametric study, the strip width as well as the gap of the inductor coil  50  was varied within the range of 10 to 15 microns and was fabricated on two separate HRSI wafers. The circuits were characterized using on-wafer RF probing techniques and a Hewlett Packard Automatic Network Analyzer (HP 8510C). The measured inductance L, peak quality factor Q, and frequency corresponding to the peak Q are summarized in Table 1 through table 4. The results show that the highest Q value is approximately 10.5 and the corresponding inductance L is about 150 nH. Q peaks at about 330 MHz. The observed Q and L values are deemed adequate for in-vivo measurements of pressure using MEMS based pressure sensors. 
     Table 5 presents measured resonant frequencies with chip capacitors which represent capacitance values corresponding to pressure changes sensed by MEMS pressure sensors wire bonded to the inductor coil. The results show that for L=150 nH and capacitance in the range of 0.3 to 4.0 pF, the resonant frequency varies from about 670 to 230 MHz which covers the range of interest for in-vivo applications. 
     Although there are many possible applications for the present invention, it will now be further described in relation to a bio-MEMS, spinal implant, pressure sensor. In a spine fusion operation it is particularly difficult to follow the subsequent progress of the operation and monitor actual loads placed on the implant and bone graft as it heals. External imaging has proven unreliable. A reliable, wireless, telemetry system is particularly needed. FIG. 9 presents a time history of the pressure experienced after a typical spine fusion operation. Of particular note is the history of pressure during the transition time period. During the time of the implantation and transition period, pressure is seen to vary significantly. However, once fusion of the bone graft is completed, the pressure settles down to a constant value as a function of time. 
     A MEMS implanted device, as illustrated in FIG. 4, is particularly suited as a “smart spinal implant” whereby MEMS chip  36  may be attached to the spine fusion graft using a suitable adhesive. Thus the time progress of the bone graft may be conveniently monitored by merely applying a time varying magnetic field to the implanted chip  36  whereby a RF signal indicating the real time, pressure measurement of the bone graft will be transmitted to and external receiver. 
     Although the invention has been described in detail with reference to the illustrated embodiments, variations and modifications exist within the scope and spirit of the invention as described and defined in the following claims.

Technology Category: h