Patent Abstract:
A system that remotely measures displacement between two objects. A passive sensor is affixed between the objects. The internal sensor uses magnetic coupling between two sensor elements to measure their relative displacement. The sensors are either a) a permeable rod and a complimentary coil in parallel with a tuning capacitor; or b) two permeable rods, each having its own surrounding coil and a tuning capacitor. One of the sensor elements is affixed to each object which is to be monitored. When an interrogating device is placed near the sensors, a resonance can be measured whose frequency characteristics change in a reproducible manner with the relative displacement of the sensors. The resulting resonance characteristics can be calibrated in such a way as to enable the displacement of the objects to be determined.

Full Description:
RELATED PATENT APPLICATION 
     This application claims the benefit of U.S. Provisional Application No. 60/200,835, filed May 1, 2000 and entitled “Passive Spinal Fusion Diagnostic System”. 
    
    
     TECHNICAL FIELD OF THE INVENTION 
     This invention relates to devices for measuring displacement, and more particularly to a wireless device that can be implanted between two adjacent objects and used to measure changes in their separation distance. 
     BACKGROUND OF THE INVENTION 
     Displacement and proximity sensors play large roles in the automotive, aerospace, food, beverage, metal, and computer industries. The increase in automation has vastly increased the demand for such sensors. This demand is due to the replacement of outdated plant equipment and the overall increase in factory automation. 
     Of the sensors in the proximity and displacement sensor market, inductive (magnetic) and photoelectric sensors are probably the most popular. Other types of displacement sensors are capacitive sensors, ultrasonic sensors, potentiometric sensors, laser sensors, and ultrasonic sensors. 
     Magnetic displacement sensors include LVDT (linear variable differential transform) sensors, hall effect sensors, and magnetostrictive sensors. LVDT sensors use three coils, a primary coil and two secondary coils. The secondary coils are connected to establish a null position. A magnetic core inside the coil winding assembly provides a magnetic flux. When the core is displaced from the null position, an electromagnetic imbalance occurs. Hall effect sensors are based on a voltage that is generated in one direction when a current and a magnetic field pass through semiconductor material in the other two perpendicular directions. 
     Variations of magnetic and inductive sensors have been developed with one or two coils. A disadvantage of many magnetic and inductive designs is the need for an electrical connection to the sensor. 
     SUMMARY OF THE INVENTION 
     One aspect of the invention is a sensor/interrogator system for measuring displacement between two adjacent objects. The sensor has a magnetic rod, a sensor coil, and a capacitor attached to the sensor coil so as to form a tuned circuit. A first end of the rod is insertable into a first end of the coil and moveable along the axis of the coil. The rod has an end mount at its second end, as does the coil, which permits the sensor to be attached between the two objects. When the objects move, the rod moves along the coil. The interrogator having at least one interrogator coil, transmit circuitry for delivering to the sensor coil an excitation signal through a range of frequencies, and receive circuitry for receiving a response signal from the sensor coil. The change in frequency of the response signal is related to the amount of motion of the rod inside the coil. 
     For orthopedic applications, an advantage of the invention is that it provides a non-invasive system that incorporates an implantable passive sensor and an external interrogating device. The system is especially useful to diagnose spinal fusion postoperatively, by measuring the changes in separation of the vertebrae. The sensor response can be correlated to the relative motion of the vertebrae. The system can also be used for diagnosing other types of bone fusion, such as motion between an orthopedic implant and the surrounding bone. Small motions in this case, indicate implant loosening. The system can also measure motion between two bone segments of a fracture. Small motions in this case, indicate non-fusion of the fracture. 
     For spinal fusion applications, when a patient postoperatively complains of pain, the physician needs to determine whether the pain is the same as the preoperative pain or if it is from a different source. The sensor/interrogator system may be used to diagnose whether the spine has fused (a new source of pain must be the cause) or not (the same area may be causing the pain). This determination will affect the patient&#39;s treatment. In addition, as the patient is monitored postoperatively, the physician can use the information from the system to guide the patient&#39;s rehabilitation program, allowing a faster recovery time and reduced healthcare costs. In the past, methods to diagnose spinal fusion have used radiographic tools. In contrast, the system described herein does not need radiography, and allows the physician to diagnose spinal fusion in his or her office. 
    
    
     BRIEF DESCRIPTION OF THE DRAWINGS 
     FIG. 1 illustrates a sensor in accordance with the invention, affixed between two vertebra of the human spine. 
     FIG. 2 illustrates a sensor similar to that shown in FIG. 1, with its rod and coil separated. 
     FIG. 3 illustrates the sensor of FIG. 2, with its rod inserted into the coil, and with the addition of a protective sheath. 
     FIG. 4 illustrates the placement of an interrogator used to transmit an excitation signal to the sensor and receive a response signal from the sensor. 
     FIG. 5 illustrates one implementation of the circuitry of the interrogator of FIG.  4 . 
     FIG. 6 illustrates an example of the signal receive circuitry of the interrogator of FIG.  5 . 
     FIG. 7 illustrates a two-coil embodiment of the interrogator of FIG.  4 . 
     FIG. 8 illustrates a three-coil embodiment of the interrogator of FIG.  4 . 
     FIG. 9 illustrates the relationship of the sensor frequency response, as detected by the interrogator, and the displacement of the sensor rod relative to the sensor coil. 
     FIG. 10 illustrates a sensor-pair configuration, which may be used as an alternative to the sensor of FIG.  1 . 
     FIG. 11 illustrates an application of the sensor-pair of FIG.  10 . 
    
    
     DETAILED DESCRIPTION 
     Single Sensor Configuration 
     FIG. 1 illustrates a displacement sensor  10  in accordance with the invention. In the example of FIG. 1, sensor  10  is used to measure displacement along the human spine and is implanted within the lumbar spine. Sensor  10  is comprised of rod  12 , coil  13 , capacitor  14 , and end mounts  15 . 
     Sensor  10  is particularly useful in environments in which wires and other types of electrical leads are impractical. As explained below, to obtain a displacement measurement, an interrogator device (not shown in FIG. 1) is placed near sensor  10 . In the orthopedic application of FIG. 1, where sensor  10  is implanted, the interrogator device is external to the body. 
     The orthopedic application of FIG. 1 is but one application of sensor  10 . In general, sensor  10  could be implanted between any two objects and used to noninvasively measure the displacement between them. For example, for structural applications, sensor  10  could be placed between blocks of a bridge or building. The size and robustness of sensor  10  is easily scaled to the type of application and to the environment in which it is to be used. 
     Regardless of the application, the objects whose displacements are to be measured are “adjacent” in the sense that an end mount  15  of sensor  10  may be attached to each object. The only limitation is that the end mounts  15  of sensor  10  each be affixed in a manner that permits sensor  10  to “bridge” the two objects and that permits coil  13  and rod  12  to move relative to each other if the objects move. The term “objects” is used herein in the broadest sense; the two “objects” between which sensor  10  is attached could be two surfaces of two different pieces of material or two surfaces of a single piece of material. 
     End mounts  15  are at either end of sensor  10 . Each end mount  15  is attached to one of two objects whose displacement is to be measured. In the example of FIG. 1, end mounts  15  are ball joints. Motion is measured along a single axis—that of the sensor  10 . There may be more degrees of freedom, but only axial motion is sensed. Screws are used to attach the end mounts  15  to the vertebrae through holes in end mounts  15 . 
     FIGS. 2 and 3 illustrate sensor  10  with its coil  13  and rod  12  segments separated and coupled, respectively. In FIG. 2, sensor  10  is shown without end mounts. FIG. 3 further illustrates a flexible sheath  21 , which may be placed over rod  12 , coil  13 , and capacitor  14 . Sheath  21  is typically used when sensor  10  is implanted for biomedical applications, such as the orthopedic application of FIG.  1 . 
     In operation, as explained below, the motion of rod  12  within coil  13  can be correlated to the relative motion of the two objects to which sensor  10  is attached. In the example of FIG. 1, the motion of rod  12  within coil  13  can be correlated to lumbar spine motion and therefore to spinal fusion success. Sensor  10  may be positioned between any two vertebrae involved in the spinal fusion or on the ends of a spinal fusion segment. More than one sensor  10  could be implanted. Sensor  10  can be attached to the anterior or anterolateral spine or the vertebral body. Sensor  10  can be attached to the posterior spine on either the spinous processes, transverse processes or the facets. Alternative attachment sites may be necessary given the specific anatomy of a patient. In the example of FIG. 1, sensor  10  is attached to the spinous processes. 
     A vast variety of attachment mechanisms can be used as end mounts  15 , such as rivets, epoxy, or spring mechanisms. End mounts  15  may themselves be some type of screw or insertion post. For some applications, the attachment means should rigidly attach sensor  10  to the objects whose displacement is to be measured, minimizing any relative motion between sensor  10  and the objects to which it is attached. For other applications, end mounts  15  might be in the form of a loop or bushing that permits slight misalignment. 
     Rod  12  is oriented along the direction of expected motion and travels along the longitudinal axis of coil  13  as motion occurs. Rod  12  is made from a magnetically permeable material such as ferrite. The optimum rod size can be determined experimentally and depends on the application; sensor  10  is easily scaled in size for different applications. The optimum rod size may involve a tradeoff between the size of the objects whose displacement is to be measured, their expected displacement, and the distance between sensor  10  and the external interrogator device. 
     For orthopedic applications, rod  12  will typically range in length from one-half inch upwards, depending on where it is attached to the spine. Its diameter will usually range from one-eighth to one-quarter inch. 
     Coil  13  is comprised of coiled wire, the diameter of which again depends on the application and other dimensions of sensor  10 . The inner diameter of coil  13  is slightly larger than the outer diameter of rod  12 . For best performance, the length of coil  13  may range from three-quarters the length of rod  12  to twice as long as rod  12 . 
     For orthopedic applications, a typical range of wire diameters is 28 AWG (American Wire Gauge) to 40 AWG. The dimensions of coil  13  might range from one-fourth to three-quarters inch long by one-eighth to three-eighths inch in internal diameter. For other applications, the dimensions of coil  13  again depend on considerations such as the environment in which sensor  10  is placed and on the expected distance from the external interrogator device. 
     Capacitor  14  is attached to coil  13 , and is chosen to set the resonant frequency of sensor  10 . A typical frequency range for various applications is 1 to 10 MHz. For this frequency range, the size of capacitor  14  might range from 50 pF to 0.01 μF. 
     A suitable capacitor size for spinal fusion applications has been determined experimentally as 220 to 1000 pF. However, for other applications, the capacitor size depends on considerations such as the maximum allowable size of the coil  13 , desired resonant frequency of sensor  10 , and the need to minimize the effects of stray capacitance on the resonant frequency. 
     Sensor  10  uses a tuned radio frequency circuit to achieve displacement measurement. The resonant frequency (f) is set by the value of an inductance (L) and the capacitance (C) of capacitor  14 , and is given by:        f   =     1     2      π        LC                                
     The inductance is determined by the plunge depth of rod  12 , which, in turn, is determined by the spacing between the two objects to which sensor  10  is attached. 
     Means other than a capacitor  14  external to coil  13  may be used to provide a resonant circuit. For example, the coil  13  could be made self resonant. Alternatively, it could be resonated with stripline, with a gyrator, or with a capacitor in the interrogator unit. Furthermore, although resonance improves the output signal, the concept of measuring relative displacement remotely using a variable magnetic coupling between two magnetically active objects may be implemented without resonance. 
     Sensor  10  is passive in that no battery or other energy source is required to power it. When excited by the interrogator device, its tuned circuit absorbs and re-radiates a signal at the sensor resonant frequency. The resonant frequency changes as the plunge depth of the rod  12  changes. This permits displacement of rod  12  within coil  13  to be inferred and used to measure displacement between the objects. For the application of FIG. 1, the spacing between vertebrae is inferred from a measurement of the resonant frequency of the tuned circuit. 
     For biomedical applications, such as the spinal application of FIG. 1, sensor  10  might be desired to be biocompatible. These considerations call for the use of biocompatible materials for each component, coating the components with a biocompatible material, or covering sensor  10  with a biocompatible cover to achieve biocompatibility. One of these methods, as well as any combination of these methods, can be used. The method chosen should not interfere with the ability of rod  12  to move within coil  13 . 
     Another consideration for biomedical and other applications that call for sensor  10  to be placed in a fluid environment, is the need to prevent shorting between the elements of sensor  10 . A sheath, such as sheath  21  of FIG. 3, may be desirable to prevent shorting and permit proper functioning. Sheath  21  may be fabricated as a rubber or plastic sleeve, latex tubing, or heat shrink coating. Biocompatible materials similar to those used for angioplasty could be used. 
     A feature of sensor  10  is that it does not interfere with normal motion of the objects to which it is attached. Specifically, for orthopedic applications, sensor  10  does not compromise the normal kinematics of the body. Sensor  10  may be attached to anatomic positions such as the spinous process or facet that will not interfere with spine motion. In addition, sensor  10  can be used with implanted fixation devices such as pedicle screw fixation systems or spinal fusion cages and can be viewed radiographically. 
     Interrogator 
     FIG. 4 illustrates interrogator  40 , placed against a patient&#39;s back during displacement measurement. Thus, for orthopedic or other biomedical applications, sensor  10  may be internal to the body, whereas interrogator  40  is external and introduced only when measurements are desired. Thus, in general, sensor  10  is not disruptive to normal movement or operation of the environment in which it is used; interrogator  40  need only be in place when measurements are to be obtained. 
     During a measurement session, interrogator  40  is placed proximate to sensor  10 . To obtain a displacement measurement, interrogator  40  “reads” sensor  10  using an interrogation coil or set of coils and appropriate circuitry. 
     The distance between interrogator  40  and sensor  10  need not remain constant in order for the system to work correctly. An increase in separation distance will result in a reduced signal, but will not affect the frequency response. 
     FIG. 5 is a block diagram of one example of interrogator  40 . It has an interrogation coil  51 , a mutual inductance bridge  52 , signal transmit and receive circuitry  53 , a swept frequency source  56 , and a driver  57 . 
     During a measurement session, interrogation coil  51  is placed sufficiently near sensor  10  so as to loosely couple the sensor coil  13  and interrogation coil  51 . The interrogation coil  51  is driven by the swept frequency source  56  through the mutual inductance bridge  52  over a frequency span that encompasses the range of possible resonant frequencies of sensor  10 . This frequency range is bounded by the frequency associated with minimum displacement and the frequency associated with maximum displacement of rod  12  relative to coil  13 . As the frequency sweeps through the resonant frequency of sensor  10 , sensor  10  absorbs and re-radiates energy, resulting in a change in the output of the mutual inductance bridge  52 . 
     FIG. 6 illustrates an example of signal transmit and receive circuitry  53 . It has a signal detector circuit  61 , an analog to digital converter  62 , a microcontroller  63 , memory  65 , and a data output interface  64 . Its functions include control of the swept frequency source  56 , calibration of the mutual inductance bridge  52 , extraction of the measured data, and formatting of the user output display. 
     In the example of FIGS. 5 and 6, frequency source  56  is a commercially available integrated circuit, but other types of frequency generation techniques may be implemented. At the receive side of interrogator  40 , the output of frequency source  56  may be mixed with the received signal for coherent detection. The amplitude of the resulting signal will then vary with frequency. This mixing technique is useful to enhance the signal to noise ratio and sensitivity of the interrogator. 
     In the example of FIG. 5, coil  51  is a single coil loop antenna that transmits an excitation signal to coil  13  and receives a response signal. In other embodiments, multiple coils (transmit and receive) could be used. Various AC coupling or mechanical nulling techniques can be used to minimize the offset portion of the signal. This permits increased gain of the received signal, and thereby increases the sensitivity of interrogator  40 . 
     FIG. 7 illustrates another example of interrogator  40 . Two coils  71  and  72  are arranged in a hull coupling geometry. The coils  71  and  72  are overlapped side by side at the critical coupling spacing so that the field from the transmit coil  71  nulls that of the receive coil  72 . A differential amplifier  73  receives and amplifies the output of the receive coil  72 . 
     FIG. 8 illustrates a three coil geometry of the interrogator  40 . Coil  81  is a transmit coil. Two receive coils  82  are connected as a differential receiver and cancel the transmitted signal. A differential amplifier  83  measures the difference between the positive signal from one receive coil  82  and the equal in amplitude but opposite in phase signal from the other receive coil  82 , and provides an amplified output of the difference. 
     For the interrogator embodiments of FIGS. 7 and 8, interrogation is accomplished by loosely coupling to sensor  10  and sweeping the frequency over the anticipated resonant frequency of the sensor. The transmit coil  71  or  81  and receive coil(s)  72  or  82  can both couple to sensor coil  13 , but not to each other. As the frequency sweeps through the resonance of sensor  10 , energy is coupled from the transmit coil  71  or  81  to the receive coils(s)  72  or  82  via the sensor&#39;s tuned circuit. The output of the receive coil(s)  72  or  82  is detected and processed as before. 
     FIG. 9 illustrates the relationship between the frequency response of sensor  10 , as detected by interrogator  40 , and the relative displacement of rod  12  relative to coil  13 . This graph shows that displacements of approximately 0.1 mm can be resolved. 
     Sensor Pair Configuration 
     FIG. 10 illustrates an alternative sensor configuration, comprised of a pair of sensors  100 . Each sensor  100  has a rod  102 , a coil  103 , and a capacitor  104 . Like sensor  10 , the rod  102 , coil  103 , and capacitor  104  form a tuned circuit. However, unlike the rods of sensors  10 , the rod  102  of a sensor  100  does not move relative to its coil  13 . It is the displacement between sensors  100  that is of interest. 
     Sensors  100  are used to measure the displacement between any two locations. One sensor  100  is attached or embedded at one location, and the other sensor  100  to a nearby location. 
     One advantage of the configuration of FIG. 10 is that the sensors  100  can be mounted independently, with no physical connection between the two. However, the sensors  100  should be initially placed sufficiently close together and in the correct orientation so as to form the overcoupled system described below. In general, the sensors  100  are placed substantially parallel to each other and offset axially. 
     Like sensor  10 , sensors  100  may each have end mounts (not shown). Furthermore, an end mount might be at only one end rather than at both ends. However, an advantage of the configuration of FIG. 10 is that sensors  100  may be simply embedded within an object or within each of two different objects; there is no need for mechanical coupling of sensors  100 . 
     For the sensor embodiment of FIG. 10, two tuned circuits are used, both to the same resonant frequency. Sensors  100  have a fixed frequency response. When placed in proximity to one another, the tuned circuits of sensors  100  interact and form an overcoupled resonant system. Rather than a single resonant peak, there is a double peak. The frequency separation between the peaks is sensitive to the spacing between the two sensors  100 . Relative motion between the sensors  100  is detectable by a shift in peak separation. 
     FIG. 11 illustrates the application of sensors  100  for measuring spinal fusion. Rods  102  are threaded on the end to allow them to be screwed directly into the spine. If a large area of the spine is of interest, numerous sensors  100  could be implanted. The relative motion of sensors  100  can be correlated to spine motion and therefore spinal fusion success. 
     The sensor-pair configuration of FIGS. 10 and 11 can be interrogated with an interrogator that is similar to interrogator  40 . The primary difference is that the data is inferred from the frequency separation of a double peak response instead of the location of a single resonant peak. 
     Orthopedic Applications 
     In practice, for orthopedic applications, one or more sensors  10  are implanted during surgery. The length of rod  12  is chosen so that at rest, rod  12  is positioned within coil  13  only one-quarter to three-quarters the length of rod  12 . For the sensor-pair configuration of FIG. 10, the two sensors  100  are placed parallel to each other and offset axially. 
     When the patient visits the physician, the interrogator  40  is secured to the patient. It is placed sufficiently close to the patient such that the distance between the sensor  10  (or sensors  100 ) and the interrogator  40  is minimized. As the patient moves, the internal sensor  101  frequency response changes will be measured and correlated to motion. 
     For the spinal fusion application of FIG. 1, theoretically, if the spinal fusion surgery was successful, there should be no measurable motion between the spinal fusion segments. The changes in the sensor response can then be correlated to relative motion of the vertebrae and to spinal fusion success. Unlike flexion-extension x-rays and CT scans which measure a static position and compare it to another static position, sensor  10  and interrogator  60  can dynamically measure motion and any sensor response changes can be correlated to fusion success. Dynamic measurement and analysis of motions are completed through automated data analysis, allowing the physician to see the outcome of the diagnostic test immediately after the test is completed. Therefore, the spinal fusion healing progression could also be objectively observed over time. 
     The same system can be used for diagnosing other types of bone fusion. For instance, the system can measure motion between an orthopedic implant and the surrounding bone. Small motions in this case would indicate implant loosening. The system can also measure motion between two bone segments of a fracture. Small motions in this case would indicate a non-fusion of the fracture. Therefore, the invention provides a very simple and consistent measuring system for diagnosing small motions between bones or between orthopedic implants and bone surfaces without being invasive. In general, the sensors are attached to “skeletal objects” whether they be natural or artificial. 
     Other Embodiments 
     Although the present invention has been described in detail, it should be understood that various changes, substitutions, and alterations can be made hereto without departing from the spirit and scope of the invention as defined by the appended claims.

Technology Classification (CPC): 0