|Publication number||US20100331733 A1|
|Application number||US 12/748,029|
|Publication date||Dec 30, 2010|
|Filing date||Mar 26, 2010|
|Priority date||Jun 30, 2009|
|Also published as||US8146422, US8245583, US8324975, US8337428, US8421479, US8424384, US8490488, US8516907, US8668646, US8689647, US8690929, US9125627, US20100326187, US20100326194, US20100326210, US20100326211, US20100327848, US20100328077, US20100328098, US20100331633, US20100331663, US20100331680, US20100331681, US20100331682, US20100331683, US20100331685, US20100331687, US20100331704, US20100331718, US20100331734, US20100331735, US20100331736, US20100331737, US20100331894, US20100332152, US20120283600, US20140135624, US20140148676|
|Publication number||12748029, 748029, US 2010/0331733 A1, US 2010/331733 A1, US 20100331733 A1, US 20100331733A1, US 2010331733 A1, US 2010331733A1, US-A1-20100331733, US-A1-2010331733, US2010/0331733A1, US2010/331733A1, US20100331733 A1, US20100331733A1, US2010331733 A1, US2010331733A1|
|Inventors||Marc T. Stein|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (6), Referenced by (18), Classifications (11), Legal Events (1)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application claims the priority benefit of U.S. provisional patent applications Nos. 61/221,761, 61/221,767, 61/221,779, 61/221,788, 61/221,793, 61/221,801, 61/221,808, 61/221,817, 61/221,867, 61/221,874, 61/221,879, 61/221,881, 61/221,886, 61/221,889, 61/221,894, 61/221,901, 61/221,909, 61/221,916, 61/221,923, and 61/221,929 all filed 30 Jun. 2009. The disclosures of which are incorporated herein by reference in its entirety.
The disclosure relates in general to orthopedics, and particularly though not exclusively, is related to measuring a parameter of a mammalian muscular-skeletal system.
The skeletal system of a mammal is subject to variations among species. Further changes can occur due to environmental factors, degradation through use, and aging. An orthopedic joint of the skeletal system typically comprises two or more bones that move in relation to one another. Movement is enabled by muscle tissue and tendons attached to the skeletal system of the joint. Ligaments hold and stabilize the one or more joint bones positionally. Cartilage is a wear surface that prevents bone-to-bone contact, distributes load, and lowers friction.
There has been substantial growth in the repair of the human skeletal system. In general, orthopedic joints have evolved as information from simulations, mechanical prototypes, and long-term patient joint replacement data is collected and used to initiate improved designs. Similarly, the tools being used for orthopedic surgery have been refined over the years but have not changed substantially. Thus, the basic procedure for replacement of an orthopedic joint has been standardized to meet the general needs of a wide distribution of the population. Although the tools, procedure, and artificial joint meet a general need, each replacement procedure is subject to significant variation from patient to patient. The correction of these individual variations relies on the skill of the surgeon to adapt and fit the replacement joint using the available tools to the specific circumstance.
Exemplary embodiments will become more fully understood from the detailed description and the accompanying drawings, wherein:
The following description of exemplary embodiment(s) is merely illustrative in nature and is in no way intended to limit the invention, its application, or uses.
Processes, techniques, apparatus, and materials as known by one of ordinary skill in the art may not be discussed in detail but are intended to be part of the enabling description where appropriate. For example specific computer code may not be listed for achieving each of the steps discussed, however one of ordinary skill would be able, without undo experimentation, to write such code given the enabling disclosure herein. Such code is intended to fall within the scope of at least one exemplary embodiment.
Additionally, the sizes of structures used in exemplary embodiments are not limited by any discussion herein (e.g., the sizes of structures can be macro (centimeter, meter, and larger sizes), micro (micrometer), and nanometer size and smaller).
Notice that similar reference numerals and letters refer to similar items in the following figures, and thus once an item is defined in one figure, it may not be discussed or further defined in the following figures.
In all of the examples illustrated and discussed herein, any specific values, should be interpreted to be illustrative only and non-limiting. Thus, other examples of the exemplary embodiments could have different values.
In at least one exemplary embodiment, an energy pulse is directed within one or more waveguides in sensor 100 by way of pulse mode operations and pulse shaping. The waveguide is a conduit that directs the energy pulse in a predetermined direction. The energy pulse is typically confined within the waveguide. In one embodiment, the waveguide comprises a polymer material. For example, urethane or polyethylene are polymers suitable for forming a waveguide. In one embodiment, the polymer waveguide can be compressed and has little or no hysteresis in the system. A transit time of an energy pulse through a medium is related to the material properties of the medium. This relationship is used to generate accurate measurements of parameters such as distance, weight, strain, pressure, wear, vibration, viscosity, and density to name but a few.
Sensor 100 can be size constrained by form factor requirements of fitting within a region of a joint of the skeletal system. In a non-limiting example, sensor 100 is used as an aid to adjust and balance a replacement knee joint. A knee prosthesis comprises a femoral prosthetic component 104, an insert, and a tibial prosthetic component 106. A distal end of femur 102 is prepared and receives femoral prosthetic component 104. Femoral prosthetic component 104 typically has two condyle surfaces that mimic a natural femur. As shown, femoral prosthetic component 104 has single condyle surface being coupled to femur 100. Femoral prosthetic component 104 is typically made of a metal or metal alloy.
A proximal end of tibia 108 is prepared to receive tibial prosthetic component 106. Tibial prosthetic component 106 is a support structure that is fastened to the proximal end of the tibia and is usually made of a metal or metal alloy. The tibial prosthetic component 106 also retains the insert in place fixed in position with respect to tibia 108. The insert is fitted between femoral prosthetic component 104 and tibial prosthetic component 106. The insert has at least one bearing surface that is in contact with at least condyle surface of femoral prosthetic component 104. The condyle surface can move in relation to the bearing surface of the insert such that the lower leg can rotate under load. The insert is typically made of a high wear plastic material that minimizes friction.
In a knee joint replacement process, the surgeon affixes femoral prosthetic component 104 to the femur 102 and tibial prosthetic component 106 to tibia 108. The tibial prosthetic component 106 can include a tray or plate affixed to the planarized proximal end of the tibia 108. Sensor 100 is placed between a condyle surface of femoral prosthetic component 104 and a major surface of tibial prosthetic component 106. The condyle surface contacts a major surface of sensor 100. The major surface of sensor 100 approximates a surface of the insert. Tibial prosthetic component 106 can include a cavity or tray on the major surface that receives and retains sensor 100 during a measurement process. Tibial prosthetic component 106 and sensor 100 has a combined thickness that represents a combined thickness of tibial prosthetic component 106 and a final (or chronic) insert of the knee joint.
In one embodiment, two sensors 100 are fitted into two separate cavities, the cavities are within a trial insert (that may also be referred to as the tibial insert, rather than the tibial component itself) that is held in position by tibial component 106. One or two sensors 100 may be inserted between femoral prosthetic component 104 and tibial prosthetic component 106. Each sensor is independent and each measures a respective condyle of femur 102. Separate sensors also accommodate a situation where a single condyle is repaired and only a single sensor is used. Alternatively, the electronics can be shared between two sensors to lower cost and complexity the circuitry of which will be disclosed in more detail hereinbelow. The shared electronics can multiplex between each sensor module to take measurements when appropriate. Measurements taken by sensor 100 aid the surgeon in modifying the absolute loading on each condyle and the balance between condyles. Although shown for a knee implant, sensor 100 can be used to measure other orthopedic joints such as the spine, hip, shoulder, elbow, ankle, wrist, interphalangeal joint, metatarsophalangeal joint, metacarpophalangeal joints, and others. Alternatively, sensor 100 can be adapted to orthopedic tools to provide measurements.
The prosthesis incorporating sensor 100 emulates the function of a natural knee joint. Sensor 100 can measure loads or other parameters at various points throughout the range of motion. Data from sensor 100 is transmitted to a receiving station 110 via wired or wireless communications. In a first embodiment, sensor 100 is a disposable system. After using sensor 100 to optimally fit the joint implant, it can be disposed of after the operation is completed. Sensor 100 is a low cost disposable system that reduces capital expenditures, maintenance, and accounting when compared to other measurement systems. In a second embodiment, a methodology can be put in place to clean and sterilize sensor 100 for reuse. In a third embodiment, sensor 100 can be incorporated in a tool instead of being a component of the replacement joint. The tool can be disposable or be cleaned and sterilized for reuse. In a fourth embodiment, sensor 100 can be a permanent component of the replacement joint. Sensor 100 can be used to provide both short term and long term post-operative data on the implanted joint. The receiving station 110 can include data processing, storage, or display, or combination thereof and provide real time graphical representation of the level and distribution of the load. Receiving station 110 can record and provide accounting information of sensor 100 to an appropriate authority.
In an intra-operative example, sensor 100 can measure forces (Fx, Fy, Fz) with corresponding locations and torques (e.g. Tx, Ty, and Tz) on the femoral prosthetic component 104 and the tibial prosthetic component 106. The measured force and torque data is transmitted to receiving station 110 to provide real-time visualization for assisting the surgeon in identifying any adjustments needed to achieve optimal joint pressure and balancing. The data has substantial value in determining ranges of load and alignment tolerances required to minimize rework and maximize patient function and longevity of the joint.
As mentioned previously, sensor 100 can be used for other joint surgeries; it is not limited to knee replacement implant or implants. Moreover, sensor 100 is not limited to trial measurements. Sensor 100 can be incorporated into the final joint system to provide data post-operatively to determine if the implanted joint is functioning correctly. Early determination of a problem using sensor 100 can reduce catastrophic failure of the joint that a patient is unaware of. The problem can often be rectified with a minimal invasive procedure at lower cost and stress to the patient. Similarly, longer term monitoring of the joint can determine wear or misalignment that if detected early can be adjusted for optimal life or replacement of a wear surface with minimal surgery thereby extending the life of the implant. In general, sensor 100 can be shaped such that it can be placed or engaged or affixed to or within load bearing surfaces used in many orthopedic applications (or used in any orthopedic application) related to the musculoskeletal system, joints, and tools associated therewith. Sensor 100 can provide information on a combination of one or more performance parameters of interest such as wear, stress, kinematics, kinetics, fixation strength, ligament balance, anatomical fit and balance.
In one embodiment, the electrical components can include ultrasound resonators or transducers, ultrasound waveguides, and signal processing electronics, but are not limited to these. The mechanical components can include biasing springs 32, spring retainers and posts, and load platforms 6, but are not limited to these. The electrical components and mechanical components can be inter-assembled (or integrated) onto a printed circuit board 36 to operate as a coherent ultrasonic measurement system within sensing module 101 and according to the sensing mode. As will be explained hereinbelow in more detail, the signal processing electronics incorporate edge detect circuitry that detects an edge of a signal after it has propagated through waveguide 5. The detection initiates the generation of a new pulse by an ultrasound resonator or transducer that is coupled to waveguide 5 for propagation therethrough. A change in transit time of a pulse through waveguide 5 is measured and correlates to a change in material property of waveguide 5.
Sensing module 101 comprises one or more assemblages 3 each comprised one or more ultrasound resonators. As illustrated, waveguide 5 is coupled between transducers 4 and 30 and affixed to load bearing or contacting surfaces 6. In one exemplary embodiment, an ultrasound signal is coupled for propagation through waveguide 5. The sensing module 101 is placed, attached to, or affixed to, or within a body, instrument, or other physical system 7 having a member or members 8 in contact with the load bearing or contacting surfaces 6 of the sensing module 101. This arrangement facilitates translating the parameters of interest into changes in the length or compression or extension of the waveguide or waveguides 5 within the sensing module or device 100 and converting these changes in length into electrical signals. This facilitates capturing data, measuring parameters of interest and digitizing that data, and then subsequently communicating that data through antenna 34 to external equipment with minimal disturbance to the operation of the body, instrument, appliance, vehicle, equipment, or physical system 7 for a wide range of applications.
The sensing module 101 supports three modes of operation of pulse propagation and measurement: reflectance, unidirectional, and bi-directional. These modes can be used as appropriate for each individual application. In unidirectional and bi-directional modes, a chosen ultrasound resonator or transducer is controlled to emit pulses of ultrasound waves into the ultrasound waveguide and one or more other ultrasound resonators or transducers are controlled to detect the propagation of the pulses of ultrasound waves at a specified location or locations within the ultrasound waveguide. In reflectance or pulse-echo mode, a single ultrasound or transducer emits pulses of ultrasound waves into waveguide 5 and subsequently detects pulses of echo waves after reflection from a selected feature or termination of the waveguide. In pulse-echo mode, echoes of the pulses can be detected by controlling the actions of the emitting ultrasound resonator or transducer to alternate between emitting and detecting modes of operation. Pulse and pulse-echo modes of operation may require operation with more than one pulsed energy wave propagating within the waveguide at equilibrium.
Many parameters of interest within physical systems or bodies can be measured by evaluating changes in the transit time of energy pulses. The frequency, as defined by the reciprocal of the average period of a continuous or discontinuous signal, and type of the energy pulse is determined by factors such as distance of measurement, medium in which the signal travels, accuracy required by the measurement, precision required by the measurement, form factor of that will function with the system, power constraints, and cost. In the non-limiting example, pulses of ultrasound energy provide accurate markers for measuring transit time of the pulses within waveguide 5. In general, an ultrasonic signal is an acoustic signal having a frequency above the human hearing range (e.g. >20 KHz) including frequencies well into the megahertz range. In one embodiment, a change in transit time of an ultrasonic energy pulse corresponds to a difference in the physical dimension of the waveguide from a previous state. For example, a force or pressure applied across the knee joint compresses wave guide 5 to a new length and changes the transit time of the energy pulse When integrated as a sensing module and inserted or coupled to a physical system or body, these changes are directly correlated to the physical changes on the system or body and can be readily measured as a pressure or a force.
In unidirectional mode, either of the ultrasound resonators or transducers for example 202 can be enabled to emit ultrasound waves 218 into the waveguide 214. The non-emitting ultrasound resonator or transducer 204 is enabled to detect the ultrasound waves 218 emitted by the ultrasound resonator or transducer 202.
In reflectance mode, the ultrasound waves 218 are detected by the emitting ultrasound resonator or transducer 202 after reflecting from a surface, interface, or body at the opposite end of the waveguide 214. In this mode, either of the ultrasound resonators or transducers 202 or 204 can be selected to emit and detect ultrasound waves. Additional reflection features 216 can be added within the waveguide structure to reflect ultrasound waves. This can support operation in a combination of unidirectional and reflectance modes. In this mode of operation, one of the ultrasound resonators, for example resonator 202 is controlled to emit ultrasound waves 218 into the waveguide 214. Another ultrasound resonator or transducer 206 is controlled to detect the ultrasound waves 218 emitted by the emitting ultrasound resonator 202 (or transducer) subsequent to their reflection by reflecting feature 216.
The use of waveguide 306 enables the construction of low cost sensing modules and devices over a wide range of sizes, including highly compact sensing modules, disposable modules for bio-medical applications, and devices, using standard components and manufacturing processes. The flexibility to construct sensing modules and devices with very high levels of measurement accuracy, repeatability, and resolution that can scale over a wide range of sizes enables sensing modules and devices to the tailored to fit and collect data on the physical parameter or parameters of interest for a wide range of medical and non-medical applications.
For example, sensing modules or devices may be placed on or within, or attached or affixed to or within, a wide range of physical systems including, but not limited to instruments, appliances, vehicles, equipments, or other physical systems as well as animal and human bodies, for sensing the parameter or parameters of interest in real time without disturbing the operation of the body, instrument, appliance, vehicle, equipment, or physical system.
In addition to non-medical applications, examples of a wide range of potential medical applications may include, but are not limited to, implantable devices, modules within implantable devices, modules or devices within intra-operative implants or trial inserts, modules within inserted or ingested devices, modules within wearable devices, modules within handheld devices, modules within instruments, appliances, equipment, or accessories of all of these, or disposables within implants, trial inserts, inserted or ingested devices, wearable devices, handheld devices, instruments, appliances, equipment, or accessories to these devices, instruments, appliances, or equipment. Many physiological parameters within animal or human bodies may be measured including, but not limited to, loading within individual joints, bone density, movement, various parameters of interstitial fluids including, but not limited to, viscosity, pressure, and localized temperature with applications throughout the vascular, lymph, respiratory, and digestive systems, as well as within or affecting muscles, bones, joints, and soft tissue areas. For example, orthopedic applications may include, but are not limited to, load bearing prosthetic components, or provisional or trial prosthetic components for, but not limited to, surgical procedures for knees, hips, shoulders, elbows, wrists, ankles, and spines; any other orthopedic or musculoskeletal implant, or any combination of these.
As illustrated, external force 408 compresses waveguide 406 and pushes the transducers 402 and 404 closer to one another by a distance 410. This changes the length of waveguide 406 by distance 412 of the waveguide propagation path between transducers 402 and 404. Depending on the operating mode, the sensing circuitry measures the change in length of the waveguide 406 by analyzing characteristics of the propagation of ultrasound waves within the waveguide.
One interpretation of
Changes in the parameter or parameters of interest are measured by measuring changes in the transit time of energy pulses or waves within the propagating medium. Closed loop measurement of changes in the parameter or parameters of interest is achieved by modulating the repetition rate of energy pulses or the frequency of energy waves as a function of the propagation characteristics of the elastic energy propagating structure.
These measurements may be implemented with an integrated wireless sensing module or device having an encapsulating structure that supports sensors and load bearing or contacting surfaces and an electronic assemblage that integrates a power supply, sensing elements, energy transducer or transducers and elastic energy propagating structure or structures, biasing spring or springs or other form of elastic members, an accelerometer, antennas and electronic circuitry that processes measurement data as well as controls all operations of ultrasound generation, propagation, and detection and wireless communications. The electronics assemblage also supports testability and calibration features that assure the quality, accuracy, and reliability of the completed wireless sensing module or device.
The sensing assembly 502 comprises transducer 4, transducer 30, and a waveguide 5 (or energy propagating structure). In a non-limiting example, sensing assemblage 502 is affixed to load bearing or contacting surfaces 508. External forces applied to the contacting surfaces 508 compress the waveguide 5 and change the length of the waveguide 5. The transducers 4 and 30 will also be moved closer together. The change in distance affects the transmit time 510 of energy waves 506 transmitted and received between transducers 4 and 30. The pulsed system 504 in response to these physical changes will detect each energy wave sooner (e.g. shorter transit time) and initiate the propagation of new pulses associated with the shorter transit time. As will be explained below, this is accomplished by way of pulse system 504 in conjunction with the pulse circuit 512, the mode control 514, and the edge detect circuit 516.
Notably, changes in the waveguide 5 (energy propagating structure or structures) alter the propagation properties of the medium of propagation (e.g. transmit time 510). A pulsed approach reduces power dissipation allowing for a temporary power source such as a battery or capacitor to power the system during the course of operation. In at least one exemplary embodiment, a pulse is provided to transducer 4 coupled to a first surface of waveguide 5. Transducer 4 generates a pulsed energy wave 506 coupled into waveguide 5. In a non-limiting example, transducer 4 is a piezo-electric device capable of transmitting and receiving acoustic signals in the ultrasonic frequency range.
Transducer 30 is coupled to a second surface of waveguide 5 to receive the propagated pulsed signal and generates a corresponding electrical signal. The electrical signal output by transducer 30 is coupled to edge detect circuit 516. In at least one exemplary embodiment, edge detect circuit 516 detects a leading edge of the electrical signal output by transducer 30 (e.g. the propagated energy wave 506 through waveguide 5). The detection of the propagated pulsed signal occurs earlier (due to the length/distance reduction of waveguide 5) than a signal prior to external forces 508 being applied to sensing assemblage 502. Pulse circuit 512 generates a new pulse in response to detection of the propagated pulsed signal by edge detect circuit 516. The new pulse is provided to transducer 4 to initiate a new pulsed sequence. Thus, each pulsed sequence is an individual event of pulse propagation, pulse detection and subsequent pulse generation that initiates the next pulse sequence.
The transit time 510 of the propagated pulse corresponds to the time from the detection of one propagated pulse to the next propagated pulse. There is delay associated with each circuit described above. Typically, the total delay of the circuitry is significantly less than the propagation time of a pulsed signal through waveguide 5. Also, under equilibrium conditions variations in circuit delay are minimal. Multiple pulse to pulse timings can be used to generate an average time period when change in external forces 508 occur relatively slowly in relation to the pulsed signal propagation time such as in a physiologic or mechanical system. The digital counter 518 in conjunction with electronic components counts the number of propagated pulses to determine a corresponding change in the length of the waveguide 5. These changes in length change in direct proportion to the external force thus enabling the conversion of changes in parameter or parameters of interest into electrical signals.
In at least one exemplary embodiment, pulsed system 504 in conjunction with one or more sensing assemblages 502 are used to take measurements on a muscular-skeletal system. In a non-limiting example, sensing assemblage 502 is placed between a femoral prosthetic component and tibial prosthetic component to provide measured load information that aids in the installation of an artificial knee joint. The measurements can be made in extension and in flexion. Assemblage 502 is used to measure the condyle loading to determine if it falls within a predetermined range and location. Based on the measurement, the surgeon can select the thickness of the insert such that the measured loading and incidence with the final insert in place will fall within the predetermined range. Soft tissue tensioning can be used by a surgeon to further optimize the force or pressure. Similarly, two assemblages 502 can be used to measure both condyles simultaneously or multiplexed. The difference in loading (e.g. balance) between condyles can be measured. Soft tissue tensioning can be used to reduce the force on the condyle having the higher measured loading to reduce the measured pressure difference between condyles.
One method of operation holds the number of pulsed energy waves propagating through waveguide 5 as a constant integer number. A time period of a pulsed energy wave corresponds to the time between the leading pulse edges of adjacent pulsed energy waves. A stable time period is one in which the time period changes very little over a number of pulsed energy waves. This occurs when conditions that affect sensing assemblage 502 stay consistent or constant. Holding the number of pulsed energy waves propagating through waveguide 5 to an integer number is a constraint that forces a change in the time between pulses when the length of waveguide 5 changes. The resulting change in time period of each pulsed energy wave corresponds to a change in aggregate pulse periods that is captured using digital counter 518 as a measurement of changes in external forces or conditions 508.
A further method of operation according to one embodiment is described hereinbelow for pulsed energy wave 506 propagating from transducer 4 and received by transducer 30. In at least one exemplary embodiment, pulsed energy wave 506 is an ultrasonic energy wave. Transducers 4 and 30 are piezo-electric resonator transducers. Although not described, wave propagation can occur in the opposite direction being initiated by transducer 30 and received by transducer 4. Furthermore, detecting ultrasound resonator transducer 30 can be a separate ultrasound resonator as shown or transducer 4 can be used solely depending on the selected mode of propagation (e.g. reflective sensing). Changes in external forces or conditions 508 affect the propagation characteristics of waveguide 5 and alter transit time 510. As mentioned previously, pulsed system 504 holds constant an integer number of pulsed energy waves 506 propagating through waveguide 5 (e.g. an integer number of pulsed energy wave time periods) thereby controlling the repetition rate. As noted above, once pulsed system 504 stabilizes, the digital counter 518 digitizes the repetition rate of pulsed energy waves, for example, by way of edge-detection, as will be explained hereinbelow in more detail.
In an alternate embodiment, the repetition rate of pulsed energy waves 506 emitted by transducer 4 can be controlled by pulse circuit 512. The operation remains similar where the parameter to be measured corresponds to the measurement of the transit time 510 of pulsed energy waves 506 within waveguide 5. It should be noted that an individual ultrasonic pulse can comprise one or more energy waves with a damping wave shape as shown. The pulsed energy wave shape is determined by the electrical and mechanical parameters of pulse circuit 512, interface material or materials, where required, and ultrasound resonator or transducer 4. The frequency of the energy waves within individual pulses is determined by the response of the emitting ultrasound resonator 4 to excitation by an electrical pulse 520. The mode of the propagation of the pulsed energy waves 506 through waveguide 5 is controlled by mode control circuitry 514 (e.g., reflectance or uni-directional). The detecting ultrasound resonator or transducer may either be a separate ultrasound resonator or transducer 30 or the emitting resonator or transducer 4 depending on the selected mode of propagation (reflectance or unidirectional).
In general, accurate measurement of physical parameters is achieved at an equilibrium point having the property that an integer number of pulses are propagating through the energy propagating structure at any point in time. Measurement of changes in the “time-of-flight” or transit time of ultrasound pulses within a waveguide of known length can be achieved by modulating the repetition rate of the ultrasound pulses as a function of changes in distance or velocity through the medium of propagation, or a combination of changes in distance and velocity, caused by changes in the parameter or parameters of interest.
It should be noted that ultrasound energy pulses or waves, the emission of ultrasound pulses or waves by ultrasound resonators or transducers, transmitted through ultrasound waveguides, and detected by ultrasound resonators or transducers are used merely as examples of energy pulses, waves, and propagation structures and media. Other embodiments herein contemplated can utilize other wave forms, such as, light.
Measurement by pulsed system 504 and sensing assemblage 502 enables high sensitivity and signal-to-noise ratio as the time-based measurements are largely insensitive to most sources of error that may influence voltage or current driven sensing methods and devices. The resulting changes in the transit time of operation correspond to frequency which can be measured rapidly and with high resolution. This achieves the required measurement accuracy and precision thus capturing changes in the physical parameters of interest and enabling analysis of their dynamic and static behavior.
A pulse method facilitates separation of ultrasound frequency, damping waveform shape, and repetition rate of pulses of ultrasound waves. Separating ultrasound frequency, damping waveform shape, and repetition rate enables operation of ultrasound transducers at or near resonance to achieve higher levels of conversion efficiency and power output thus achieving efficient conversion of ultrasound energy. Likewise, separating frequency and repetition rate enables control of damping factors within pulses of ultrasound waves by selecting frequencies at some distance from the resonance points of the ultrasound transducers. This may enable, but is not limited to, lower power operation for ultra-low power devices.
In a non-limiting example, a pulse mode operation is initiated with control circuitry 606 closing switch 604, which couples an output of pulse circuit 608 to an input of amplifier 612. Pulse circuit 608 initializes the circuit by sending one or more pulses to amplifier 612. Amplifier 612 provides analog pulses 614 to an input of transducer 4. Amplifier 612 having digital driver 642 and matching network 644 transforms the digital output (e.g. square wave) of pulse circuit 610 into shaped or analog pulses 614 that are modified for emitting transducer 4. The repetition rate of pulses 614 is equal to the pulse rate at output 610 of pulse circuit 612. Amplifier 612 drives transducer 4 with sufficient power to generate energy waves 616. In at least one exemplary embodiment, transducer 4 converts the pulsed electrical waves into pulsed energy waves 616 having the same repetition rate and emits them into energy propagating structure or waveguide 5. In a non-limiting example, energy waves 616 are ultrasound waves.
In general, ultrasound transducers naturally resonate at a predetermined frequency. Providing a square wave to the input of emitting transducer 4 could yield undesirable results. Digital driver 642 of amplifier 612 drives matching network 644. Matching network 644 is optimized to match an input impedance of emitting transducer 4 for efficient power transfer. In at least one exemplary embodiment, digital driver 642, matching network 644, solely, or in combination shapes or filters pulses provided to the input of amplifier 612. The waveform is modified from a square wave to analog pulse 614 to minimize ringing and to aid in the generation of a damped waveform by emitting transducer 4. In one embodiment, the pulsed energy wave emitted into waveguide 5 can ring with a damped envelope that affects signal detection which will be disclosed in more detail below.
The one or more pulsed energy waves 616 propagate through energy propagating structure or medium 5 and are detected by detecting transducer 30. Detecting transducer 30 converts the pulsed energy waves 616 into pulses 618 of electrical waves having the same repetition rate. The signal output of detecting transducer 30 may need amplification. Amplifier 620 comprises pre-amplifier 622 and edge-detect receiver 624. Pre-amplifier 622 receives and amplifies analog pulses 618 from transducer 30. Edge-detect receiver 624 detects an edge of each arriving pulse corresponding to each propagated pulsed energy wave 616 through waveguide 5. As mentioned previously, each pulsed energy wave can be a ringing damped waveform. In at least one exemplary embodiment, edge-detect receiver 624 detects a leading edge of each arriving pulse 618. Edge-detect receiver 624 can have a threshold such that signals below the threshold cannot be detected. Edge-detect receiver 624 can include a sample and hold that prevents triggering on subsequent edges of a ringing damped signal. The sample and hold can be designed to “hold” for a period of time where the damped signal will fall below the threshold but less than the shortest edge to edge time period between adjacent pulses under all operating conditions. Amplifier 620 generates a digital pulse 626 triggered off of each leading edge of each propagated pulsed energy wave 616 detected by transducer 30. Each digital pulse 626 is of sufficient length to sustain the pulse behavior of the closed loop circuit as it is coupled back to amplifier 612 through switch 628.
Control circuitry 606 responds to the initial digital output pulses 626 from amplifier 620 by closing switch 628 and opening switch 604. Closing switch 628 creates a positive feedback closed loop circuit coupling a pulse generated by amplifier 620 to the input of amplifier 612 and sustaining a sequence of pulsed energy wave emission into wave guide 5, propagation of the pulsed energy wave 616 through waveguide 5, detection of the pulsed energy wave after traveling through waveguide 5, and generation of the next digital pulse.
In one embodiment, the delay of amplifier 620 and 612 is small in comparison to the propagation time of a pulsed energy wave through waveguide 5. In an equilibrium state, an integer number of pulses of energy waves 616 in waveguide 5 have equal time periods and transit times when propagating through energy propagating structure waveguide 5. For example, three pulsed energy waves propagate through waveguide 5. As one energy pulse wave exists waveguide 5, a new energy pulse wave is emitted into waveguide 5 as electronic circuitry comprised of amplifier 620 and 612, having little or no delay, maintain equilibrium. Movement or changes in the physical properties of the energy propagating structure or waveguide 5 change the transit time 630 of energy waves 616. This disrupts the equilibrium thereby changing when a pulsed energy wave is detected by edge-detect receiver 624. A transit time is reduced should external forces 632 compress waveguide 5 in the direction of propagation of energy waves 616. Conversely, the transit time is increased should external forces 632 result in waveguide 5 expanding in length. The change in transit time delivers digital pulses 626 earlier or later than previous pulses thereby producing an adjustment to the delivery of analog pulses 618 and 614 to a new equilibrium point. The new equilibrium point will correspond to a different transit time, e.g. different repetition rate with the same integer number of pulses.
As previously disclosed, the repetition rate of energy waves 616 during operation of the closed loop circuit, and changes in this repetition rate, can be used to measure changes in the movement or changes in the physical attributes of energy propagating structure or medium 5. The changes can be imposed on the energy propagating structure or medium 5 by external forces or conditions 632 thus translating the levels and changes of the parameter or parameters of interest into signals that may be digitized for subsequent processing, storage, and display. Thus, the repetition rate of pulses of energy waves 616 during the operation of the closed loop circuit, and changes in this repetition rate, can be used to measure movement or changes in physical attributes of energy propagating structure or medium 5.
The changes in physical attributes of energy propagating structure or medium 5 by external forces or conditions 632 translates the levels and translates the parameter or parameters of interest into a time period difference of adjacent pulses or a difference accumulated or averaged over multiple time periods. The time period of transit time 630 corresponds to a frequency for the time period measured. The time period can be digitized for subsequent transmission, processing, storage, and display. Translation of the time period into digital binary numbers facilitates communication, additional processing, storage, and display of information about the level and changes in physical parameters of interest. Prior to measurement of the frequency of operation of the pulse sequence generation circuitry, control logic 606 loads the loop count into digital counter 638 that is stored in digital register 640.
Digital logic circuit 675 is described in more detail hereinbelow. As previously mentioned, a first pulse from digital pulses 610 initiates a parameter measurement or sensing of waveguide 5. In at least one exemplary embodiment, sensing does not occur until initial equilibrium has been established. Control circuit 606 detects digital pulses 626 from amplifier 620 (closing switch 628 and opening switch 604) to establish equilibrium and start measurement operations. In an extended configuration of pulse-loop mode, a digital block is coupled to the pulsed-loop mode measurement system for digitizing the frequency of operation. Translation of the time period of pulsed energy waves into digital binary numbers facilitates communication, additional processing, storage, and display of information about the level and changes in physical parameters of interest. During this process, control circuit 606 enables digital counter 638 and digital timer 634. Digital counter 638 decrements its value on the rising edge of each digital pulse 626 output by amplifier 620. Digital timer 634 increments its value on each rising edge of pulses from clock output 610. A clock such as a crystal oscillator is used to clock digital logic circuit 675 and as a reference in which to gauge time periods of pulsed energy waves. Alternatively, pulse circuit 608 can be a reference clock. When the number of digital pulses 626 has decremented the value within digital counter 638 to zero a stop signal is output from digital counter 638. The stop signal disables digital timer 634 and triggers control logic 606 to output a load command to data register 636. Data register 636 loads a binary number from digital timer 634 that is equal to the period of the energy waves or pulses times the value originally loaded into counter 638 divided by a clock period corresponding to oscillator output 610. With a constant clock period, the value in data register 636 is directly proportional to the aggregate period of the pulsed energy waves or pulses accumulated during the measurement operation. Duration of the measurement operation and the resolution of measurements may be adjusted by increasing or decreasing the value preset in the count register 640.
This method of operation further enables setting the level of precision or resolution of the captured data by using long cycle counts to optimize trade-offs between measurement resolution versus pulse repetition rate, ultrasound frequency, and damping waveform shape, as well as the bandwidth of the sensing and the speed of the data processing operations to achieve an optimal operating point for a sensing module or device that matches the operating conditions of the system containing, or subject to, the parameter or parameters of interest.
In at least one exemplary embodiment, the sensor system includes the system as a wireless module that operates according to one or more criteria such as, but not limited to, power level, applied force level, standby mode, application context, temperature, or other parameter level. Pulse shaping can also be applied to increase reception quality depending on the operational criteria. The wireless sensing module comprises the pulsed measurement system, one or more sensing assemblies, one or more load surfaces, an accelerometer, electronic circuitry, a transceiver, and an energy supply. The wireless sensing module measures a parameter such as force/pressure and transmits the measurement data to a secondary system for further processing and display. The electronic circuitry in conjunction with the sensing assemblies accurately measures physical displacements of the load surfaces on the order of a few microns or less along various physical dimensions. The sensing assembly physically changes in response to an applied force, such as an applied load. Electronic circuitry operating in a positive feedback closed-loop circuit configuration precisely measures changes in propagation time due to changes in the length of the waveguides; physical length changes which occur in direct proportion to the applied force.
In a non-limiting example, an ultrasound signal is used in the measurement system. For illustration purposes the measurement system measures a load, pressure, or force. The system has two surfaces to which the measured parameter (e.g. load, pressure, force) can be applied. In one embodiment, one of the surfaces is in a fixed position and the measured parameter is applied to the remaining surface. Alternatively, the measured parameter can be applied across both surfaces. In one embodiment, the system will measure within a range of 3-60 pounds.
The sensing element comprises two piezoelectric transducers and a medium. One or more sensing elements can be used. The sensing element is placed between the surfaces of the measurement system. In one embodiment, the waveguide comprises a polymer such as urethane or polyethylene. In a non-limiting example, the polymer can be stretched or compressed when subjected to the parameter under measurement and has little or no hysteresis in the system. In general, the waveguide efficiently contains and directs an ultrasonic pulsed energy wave such that a measurement of either the transit time of the pulsed energy wave to propagate through the waveguide or time period of the pulsed energy wave can be taken. The waveguide can be cylindrically shaped having a first end and a second end of the cylinder. The piezoelectric transducers are attached at the first and second ends of the waveguide to emit and receive ultrasonic pulsed energy waves. The transducers are attached to be acoustically coupled the waveguide and can have an intermediate material layer to aid in improving the transfer of the ultrasonic pulsed energy wave.
In the non-limiting example, the waveguide in a relaxed state is a cylinder or column 47 millimeters long which can accommodate one or more ultrasonic pulsed energy waves. The length of the waveguide corresponds to the thickness of the sensor and is thus an indication that a very small form factor sensor can be built using this methodology. In one embodiment, the waveguide is placed in a compressed state in the sensor module. In the non-limiting example, the waveguide is subjected to a force or pressure that changes the dimensions of the cylinder. More specifically, an applied force or pressure on the surfaces of the system modifies the length of the waveguide. In one embodiment, the waveguide is compressed from the 47 millimeter relaxed state to a thickness of approximately 39 millimeters. The 39 millimeter compressed state corresponds to the state where no load is applied to the surfaces of the sensor module.
In the non-limiting example, the emitting piezoelectric transducer has a different resonant frequency than the receiving piezoelectric transducer. The emitting piezoelectric transducer has a resonance frequency of approximately 8 megahertz. It has a diameter of approximately 3.3 millimeters and is approximately 0.23 millimeters thick. The receiving piezoelectric transducer has a resonance frequency of approximately 10-13 megahertz. It has a diameter of 4 millimeters and is approximately 0.17 millimeters. In one embodiment, the waveguide has a diameter greater than or equal to the diameter of the largest piezoelectric transducer. In the example, the waveguide would have a diameter greater than or equal to 4 millimeters.
The sensing module can very accurately measure transit time or a time period of the pulsed energy wave as disclosed hereinabove. In at least one exemplary embodiment, a single pulsed energy wave can be used to take a measurement thereby minimizing energy usage. Alternatively, more than one measurement can be taken sequentially, periodically, or randomly depending on the application requirements. The measured transit time or time period corresponds to the length of the medium or waveguide. The transit time or time period is correlated to a force or pressure required to compress the waveguide by the measured amount. Preliminary measurements indicate that the sensing module can detect changes in the length of the waveguide on the order of submicrons. Thus, the sensing module can measure the force or changes in force with high precision.
Upon reviewing the aforementioned embodiments, it would be evident to an artisan with ordinary skill in the art that said embodiments can be modified, reduced, or enhanced without departing from the scope and spirit of the claims described below. As an example:
Changing repetition rate or wave composition of complex waveforms to measure time delays.
Changing repetition rate of acoustical, sonic, or light, ultraviolet, infrared, RF or other electromagnetic waves, pulses, or echoes of pulses to measure changes in the parameter or parameters of interest.
While the present invention has been described with reference to exemplary embodiments, it is to be understood that the invention is not limited to the disclosed exemplary embodiments. The scope of the following claims is to be accorded the broadest interpretation so as to encompass all such modifications and equivalent structures and functions.
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|Cooperative Classification||Y10T307/615, A61B5/4509, A61B5/4528, A61B5/6846, A61B5/7239, A61B8/15, A61B5/6878|
|European Classification||A61B5/68D, A61B5/45K|
|Mar 26, 2010||AS||Assignment|
Owner name: ORTHOSENSOR, FLORIDA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:STEIN, MARC;REEL/FRAME:024327/0720
Effective date: 20100326