|Publication number||USRE39961 E1|
|Application number||US 10/426,249|
|Publication date||Dec 25, 2007|
|Filing date||Apr 29, 2003|
|Priority date||Jun 27, 1996|
|Also published as||US6113642|
|Publication number||10426249, 426249, US RE39961 E1, US RE39961E1, US-E1-RE39961, USRE39961 E1, USRE39961E1|
|Inventors||Steven H. Petrofsky, William G. Gruesbeck|
|Original Assignee||össur hf|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (97), Non-Patent Citations (6), Referenced by (40), Classifications (29), Legal Events (1)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application is a continuation-in-part of application Ser. No. 08/883,614, Filed Jun. 26, 1997, now U.S. Pat. No. 5,888,212. This application also claims the benefit of prior application Ser. No. 60/020,904, Filed Jun. 27, 1996. This application is a continuation of application 10/237,571, filed 5 Sep. 2002 (abandoned), which is a reissue of U.S. Pat. No. 6,113,642, issued 5 Sep. 2000, which is a continuation-in-part of application 08/883,614, filed 26 Jun. 1997 (now U.S. Pat. No. 5,888,212 ), which claims the benefit of provisional application 60/020,904, filed 27 Jun. 1996.
The present invention is ideally suited for use with an artificial leg or prosthesis worn by an above knee amputee, but also has other applications and uses. Normally this type of prosthesis involves an artificial knee joint including a socket for receiving and engaging the stump of the user, a knee bracket rigidly connected to the socket, and a frame which extends downwardly from the bracket and is pivotally connected to the bracket by a horizontal shaft. A pylon and artificial foot are connected to the base of the frame, and a control unit is connected for locking the knee joint to prevent it from buckling under load in the stance phase of a step, and for freeing the knee joint in the swing phase of the step. Preferably, the prosthesis controls the knee joint in such a way that the amputee will walk with a normal or natural appearing gait. This gait is characterized by almost identical movements performed by both lower limbs at varying walking speeds.
The biological or natural knee joint is powered by the actions of muscles. Each muscle develops an active force by contraction and also provides variable stiffness or resistance. It has not been feasible to duplicate muscle contraction in leg prosthesis because of the weight and bulk that would be required to duplicate this function. Research has focused on implementing stiffness or resistance to rotation of the knee joint. Usually this involves switching the knee joint between one of two modes, locked or free to rotate. The locked mode occurs during the stance phase of the gait cycle, and the free to rotate mode occurs during the swing phase of the gait cycle. The stance phase applies when the foot of the prosthesis is on the ground, and the swing phase applies during the time when the foot of the prosthesis is off the ground.
Much of the research in recent years has sought improvements in controlling an artificial knee joint as a way to improve gait and enable the amputee to deal with situations such as descending stairs or ramps, or lowering into a sitting position. If a knee joint is considered a simple hinge, there are two separate actions which occur. During flexion, the upper and lower segments move closer together during rotation of the knee joint. During extension, the leg straightens and the segments move apart. For a prosthetic knee joint to duplicate a biological knee, it is necessary to control the resistance to rotation in each direction independently and variably. This resistance to rotation during swing phase can be accomplished with a mechanical damper or friction device, a pneumatic damper, or a hydraulic damper. It is generally accepted in prosthetics that a hydraulic damper provides the smoothest action over a wider range of walking speeds.
Stance phase control must provide a very high resistance to flexion or lock completely any rotation to flexion. Stance control is usually provided by a weight activated mechanical locking brake mechanism, or a position activated polycentric linkage system, or a position activated hydraulic damper. Mechanical braking mechanisms can be difficult to keep adjusted properly and can cause the amputee to walk with a slightly unnatural gait. Position activated polycentric mechanisms require more concentration and can be difficult for amputees to use in some situations. Hydraulic dampers, while providing a more natural gait, require more concentration and training for the amputee.
U.S. Pat. Nos. 5,405,409 and 5,443,521, which issued to the assignee of the present invention, disclose a linear type hydraulic damper for controlling an above knee prosthesis. This hydraulic damper has independently adjustable and variable resistance in flexion and extension during the swing phase of the gait cycle. Because of the turbulent flow of the hydraulic fluid during the swing phase, this damper can accommodate a wide variation of gait speeds. The control damper has a single damping rate in stance phase that can be manually adjusted for each amputee's need. When the knee joint is fully extended, the damper assumes a non-stance resistance mode. This position activated stance phase can initially require extra gait training and concentration on the part of the amputee to receive full benefit of the damper.
Electronics have recently been introduced into lower extremity prosthetics in an attempt to make walking easier for the amputee. For example, U.S. Pat. No. 5,062,856 and U.S. Pat. Nos. 5,383,939 and 5,571,205 disclose two systems which use a microprocessor control to adjust the resistance in a pneumatic or hydraulic cylinder during swing phase in an attempt to provide control of rotation of the knee joint over a wider range of walking speeds than is available with standard pneumatic or friction dampers.
Further improvement in amputee gaits could come from a mechanism that in the beginning of the stance phase would allow for a small amount of knee flexion and then lock against further flexion while simultaneously allowing for knee extension as the leg straightens due to body action. Such a mechanism is described by Siegmar et al in “Design Principles, Biomechanical Data and Clinical Experience with a Polycentric Knee Offering Controlled Stance Phase Knee Flexion: A Preliminary Report”, Journal of Prosthetics and Orthotics, Vol. 9, No. 1, pp. 18-24, Winter 1997, and by Popvic et al in “Optimal Control for an Above-knee Prosthesis with Two Degrees of Freedom”, J. Biomechanics, Vol. 28 No. 1, pp. 89-98, 1995.
An amputee needs different resistance to knee flexion during stair descent than is needed while sitting down in a chair. Accordingly, it is desirable for a control mechanism to be capable of providing these different resistances to knee flexion automatically. The control mechanism should also provide for swing resistance over a wide range of gait speeds. All of this should happen automatically so that the amputee can walk without having to think about his prosthesis.
The same type of computer controlled hydraulic damper system that can be used with amputees can also be used on other applications such as robotics, braking systems, and exercise equipment. These applications only vary in the size of the actuator to control the maximum resistance applied. They all may use common sensors, microprocessor controlled electronics, and valve technology. Computer controlled exercise equipment are disclosed in U.S. Pat. Nos. 4,354,676, 4,711,450, 4,919,418, 5,230,672, and 5,397,287. In any such equipment, it is desirable to be able to maintain accurate applied resistance over a wide range of temperature and manufacturing tolerances. It is also desirable to have proper feedback control and a hydraulic valve and controller designed for relatively slow speeds of operation.
The present invention is directed to a computer controlled closed-loop electromechanical resistance device. One application of the device is to provide swing resistance to the knee unit of a lower limb prosthesis as worn by an above-knee amputee. Other applications for the invention include rehabilitation equipment, exercise equipment, braking devices or other various damping applications.
In accordance with a preferred embodiment of this invention, the device comprises a rotary paddle or vane type rotor or actuator. When the rotary vane is rotated, hydraulic fluid is forced through an electronically controlled valve from one side of the vane to the opposite side of the vane. As rotation is reversed, the hydraulic fluid reverses direction and flows back through the same valve. Computer control of the valve creates a variable pressure differential from one side of the rotary vane to the other side. The variable pressure differential is sensed as a variable resistance on the rotary vane. However, the resistance device of the invention may also be utilized with a linear type of actuator with equal effectiveness.
The valve used in one embodiment of the device is a proportional controlled, solenoid actuated, balanced spool valve. The shape of the spool is such that flow across the face of the spool has little or no effect on spool movement, thus eliminating any possibility of unbalanced flow induced forces. The valve spool is also pressure balanced to eliminate any possibility of a hydraulic lock. The magnetic core for the valve is shaped to produce a near constant force in the working stroke of the spool when constant power is supplied. In another embodiment, a two stage poppet or pilot operated valve is used to increase the servo valve dynamic range and to reduce significantly the unbalanced forces applied. Valve control includes a high frequency dithering to avoid spool drag, and proportional control is provided to minimize wear rate as normally associated with a pulse width modulated control.
The valve control used in the device is a microprocessor based closed loop adaptive control. The microprocessor reads actuator or rotor vane pressure differential, rotor position, auxiliary force and pressure differential error at 1-5 ms intervals (200-1000 Hz). The microprocessor calculates rotor position, rotor velocity, and rotor direction at 10-25 ms intervals (40-100 Hz). Based on this information, the microprocessor calculates the required rotor resistance (pressure differential) based on state equations, thus creating an automatically adjusting resistance device. If the difference between the actual and required pressure differential is large, the microprocessor changes the valve in large increments to compensate for this large error. If the difference between the actual and required pressure differential is small, the microprocessor changes the valve in smaller increments to compensate for this small error. By utilizing pressure feedback for the closed loop control, the control system is able to compensate automatically for machining tolerances, valve solenoid resistance variations, different fluid viscosity, temperature effects and wear. Constants in the state equations adapt with changes in the system operating environment for adaptive control.
When the device of the invention is used as a knee control unit for an above knee amputee, the control unit detects five significant points in a typical gait cycle. The two major areas of a gait cycle are stance phase and swing phase. Stance phase is the time in which the prosthesis is in contact with the ground. Swing phase is the time in which the prosthesis is not in contact with the ground. The first major point considered is heel strike which is the beginning of the stance phase. This is the point at which the prosthesis first contacts the ground and is no longer swinging in the air. The prosthesis must have stability at this point so that it will not collapse as the amputee's weight is transferred from the opposite leg.
A yielding stance is ideal for this situation in which a high resistance is applied to support the amputee, but allowing the prosthesis to flex slightly. Ideally, the prosthesis should flex about ten degrees so that the amputee does not have to vault over a fully extended prosthesis. This ten degree flexion during stance is the second point of consideration. At this point, the prosthesis begins to extend as the amputee propels himself forward. The prosthesis fully extends during this propulsion. After propulsion, the third point is the initiation of flexion in which the amputee begins to move the prosthesis forward by flexing of the hip. The fourth point is toe off in which the prosthesis leaves the ground. This is the start of swing phase.
During the swing phase, the knee control unit offers significant resistance to limit the swing speed and the amount of angular movement of the lower section of the prosthesis. Ideally, the knee should flex no more than sixty-five degrees during swing phase. This may be achieved by introducing a high resistance to limit the amount of heel rise. Due to the momentum of the prosthesis, the knee control unit begins to extend while swinging through the air. The fifth point of consideration is terminal deceleration. This occurs just prior to flee strike during the final few degrees of extension in which a high resistance must be applied to limit any harsh knee slap as the prosthesis contacts the extension stops.
To control the knee control unit, the microprocessor of the invention reads rotor vane pressure differential, knee position, pressure differential error and prosthetic force at 1-5 ms intervals (200-1000 Hz). The microprocessor calculates the knee position, knee velocity, knee direction and reads user settings (1-10) for flexion and extension at 10-25 ms intervals (40-100 Hz). The user settings for flexion and extension set an area for use, and the adaptive control fine tunes the unit from this baseline. Based on this information, the microprocessor calculates the required knee resistance (pressure differential) required based on state equations, thus creating an automatically adjusting knee control unit.
Constants in the state equations are able to adapt with changes in the system operating environment. If the difference between the actual and required pressure differential is large, the microprocessor changes the valve in large increments to compensate for this large error. If the difference between the actual and required pressure differential is small, the microprocessor changes the valve in smaller increments to compensate for this small error. If the knee angle is extending and nearing full extension, the microprocessor starts to close the valve to create a high resistance and slow the prosthesis in the extension direction. When the knee angle is flexing and nearing the ideal heel rise, the microprocessor starts to close the valve to create a high resistance and slow the prosthesis in the flexion direction. The prosthetic measured force allows the microprocessor to distinguish between heel strike, mid-stance, or toe off. This aids the amputee in descending stairs by creating a high knee resistance and lowering the amputee to the next stair by using his own weight.
Stumble recovery is achieved by sensing force and knee pivoting velocity. If the force sensors indicate a stance phase and knee velocity is high, this might indicate a stumble condition so that the system imposes a high resistance to help the amputee regain control. In the case of prolonged nonuse of greater than 5 seconds, the microprocessor reverts to sleep mode in which all components are shut down except the knee angle sensor circuit. This conserves battery power, but permits the control system to resume with a change in knee angle. Power is supplied to the control system by four 3.6 volt lithium ion batteries in a replaceable battery pack which is rechargeable to ninety percent capacity in two hours. Battery lift is approximately thirty hours between full recharges.
Preferably, the knee control unit operates with a rotary vane rotor positioned inside a rotor housing on the knee axis, and the knee bracket is connected to the rotary vane. As the knee is flexed, the vane rotates forcing hydraulic fluid out of the chamber through the solenoid control valve which in turn controls the fluid flow and pressure. This control of the fluid flow and pressure provides the resistance available at the knee axis. Fluid exiting the solenoid control valve flows through a weight actuated stance valve. This valve limits fluid flow whenever weight is applied to the prosthesis. The stance valve is adjustable to allow various yielding rates depending upon the amputees weight or preference. Fluid exiting the stance valve enters an extension bias cylinder. This cylinder consists of a spring loaded piston which is compressed when the knee control unit is flexed. Fluid on the opposite side of the bias piston is directed to the opposite side of the rotary vane, thus completing the fluid path. During extension, the flow is reversed with the stored potential energy of the spring biased piston available to assist in extending the prosthesis.
Other features and advantages of the invention will be apparent from the following description, the accompanying drawings and the appended claims.
In reference to
The knee control assembly or unit 2 is described in connection with
During knee flexion, the rotor 20 is rotated with the knee bracket 6 and rotor shaft 9, thus forcing hydraulic fluid out of rotor chamber 26 (
Passage 33 extends to an extension pressure sensor 34 (
An annular support 50 defines the chamber 40 and forms a bottom seat for the annular seal 41 and piston on the stance valve tube 38 which has an upper end pressed into a hub on the spring seat member 44. Bias cylinder leakage is controlled by a series of O-rings (FIG. 5), and hydraulic fluid is forced upwardly out of chamber 45 in response to upward movement of the annular piston 42. The fluid travels through ports within the spring seat member 44 and the upper cap 37, through a return tube 57 (
During the stance phase of gait, the amputees weight is applied to the bottom of the knee control unit 2 at a bottom plate 64 (
By adjusting the stance adjusting screw 69, the radial ports in the stance valve cap 70 may be adjusted to limit the closing of the ports during stance thus allowing a controlled leakage in the flexion direction giving the amputee a yielding stance. Extension is not affected during stance due a Belleville washer 71 above a stance check valve washer 72 that covers axial ports in the stance valve cap 70. When extension is performed during the stance phase, the hydraulic flow lifts the stance washer 72 while compressing the Belleville washer 71 to uncover the axial ports in the stance valve cap 70. When flexion is attempted during stance, hydraulic pressure will force the stance washer 72 to cover the holes in the stance valve cap 70 thus prohibiting any flexion flow moving through the stance valve end cap 70. When the load is removed from the bottom plate 64, the stance valve 39 is forced into the open position (
A block diagram for generally illustrating the hydraulic system is shown in FIG. 14. By turning the rotor 20 clockwise within the housing 15, hydraulic fluid from chamber 26 is forced through a port to the solenoid control valve 32. The solenoid control valve 32 is electronically operated for variably changing the flow area of the fluid path. By reducing the flow area in the valve 32, the hydraulic flow is reduced while back pressure is increased. This is felt as rotational resistance on the rotor shaft 9. Fluid exits the solenoid control valve 32 through a passage which leads to the stance valve member 39.
The stance valve 39 is actuated when an external force is applied. In parallel with the stance valve 39 is the check valve 72 which prevents flow with clockwise rotation of the rotor 20 when the stance valve 39 is actuated while still allowing flow with counterclockwise rotation. Also in parallel with the stance valve 39 is an adjustable orifice 78 which allows a small controlled flow during clockwise rotation when the stance valve 39 is actuated. Hydraulic fluid exits the stance valve 39 through the radial ports which permits the fluid to move or actuate the piston 42.
The piston 42 separates two chambers 40 and 45 in the cylinder 46. As fluid enters chamber 40, the piston 42 compresses the spring 43. The piston then forces fluid in chamber 45 to exit the cylinder 46. This flow returns to rotor chamber 25 to rotate the rotor clockwise. When the clockwise rotation of the rotor 20 and shaft 9 is released, the bias spring 43 and piston 42 force the hydraulic fluid out of the chamber 40 through the stance valve 39 and back through the solenoid control valve 32 and into chamber 26 resulting in a counterclockwise rotation of the rotor 20 and rotor shaft 9.
An exterior view of the solenoid control valve 32 is shown in
A valve member or valve spool 108 seats on top of a return spring 109, and a tubular spool seat 110 rests on the flux core 104 and is held in place by a tubular cartridge 111. The spool seat 110 limits the travel or axial movement of the spool 108. A cartridge plug 112 is pressed into the cartridge 111 which is threaded into the case 105. A magnetic material, such as low carbon steel, is used for the flux core 104, case 105, adjusting screw 106 and spool 108. These metal parts are preferably hyper annealed for best performance. A nonmagnetic material, such as a 300 series stainless steel, is used for the spool seat 110, cartridge plug 112 and the cartridge 111.
The solenoid control valve 32 is normally open when no power is applied to the coil 101. As power is applied, the coil 101 produces a magnetic flux which pulls the spool 108 further into the flux core 104 against the increasing force of the spring 109. The specific shape of the flux core 104 and spool 108 along with the spring rate of the spring 109 is such that spool movement is proportional to the power applied, this translates to a proportional flow control. As hydraulic fluid enters passage 30b from chamber 29, the fluid is directed from port 113 to port 114 which are formed by the cartridge 111 and the cartridge sleeve 112. If the coil 101 is fully energized, the spool 108 will close off ports 113, 117 and 114 and 116 and the flow will stop. If the coil 101 is partially energized or non-energized, the flow will then enter the spool chamber 115, flow around the spool 108 and exit through port 114 and passage 34 to tube 35.
The pair of ports 113 and 117 and the pair of ports 114 and 116 are at the same level with the ports of each pair spaced 180 degrees from each other, and with each pair of ports spaced 90 degrees from the other pair. The solenoid control valve 32 has two inlet ports 113 and 117 and two outlet ports 114 and 116, although more ports may be used if desired. Although ports 113 and 117 are described as the inlet, and ports 114 and 116 are described as the outlet, the flow may be unidirectional or bidirectional with the same results. The shape of the spool 108 in the flow area 115 provides for counterbalancing any fluid forces that may tend to open or close the spool. The spool 108 has an axial bore or hole through its center to prevent hydraulic lock. The advantages of an optimized magnetic flux to match the spring rate and an optimized spool to match fluid forces greatly reduces the power required to operate the valve. Leakage between the inlet and outlet ports is controlled by O-ring 120 mounted on the cartridge 111. External leakage of hydraulic fluid is controlled by O-rings 121 and 122. Although the solenoid control valve 32 is preferably proportionally controlled, it may also be operated with pulse width modulation.
As mentioned above, the computer controlled hydraulic resistance device of the invention has many applications, such as the knee control described above for above-knee amputees, advanced exercise systems using computer controlled resistance, and robotics or damper applications. While a complete application of an electronic knee control is disclosed herein, the use of the device in other applications is apparent.
In all applications of the device, the microprocessor 200 executes its program requiring both sensing and control in a closed-loop manner. The system programs cause a resistance to be applied to the device depending on the sensed position and velocity. Using a hydraulic fluid system, the resistance is applied by a hydraulic actuating device 211 which may be either a rotary vane such as the rotor 20 or a linear movable piston within a cylinder. The resistance is applied by restricting the flow in a closed fluid system by a solenoid control valve 210, such as the valve 32, operated by the microprocessor 200 and its control circuitry 207. The mechanical resistance is applied to a device 215 through a coupler 214. The applied device may be, for example, a knee joint of a prosthesis or a piece of exercise equipment, or a robotics platform which requires restriction in movement and/or velocity.
The position of the applied device is sensed by 216 which may be a potentiometer, proximity detector or a linear hall effect sensor such as the sensor 18. The output of the position sensor is a signal conditioned and scaled by circuitry 204. The analog position signal leaving 204 is converted to digital 8-16 bit number by the microprocessor's A/D converter or an external A/D device for use in the main program. The position is time sampled at fixed intervals. The difference in position between the fixed intervals of time divided by the time sample duration is the velocity of the device movement to be also used by the main program as well as the direction of movement.
To produce the calculated desired resistance to the applied device with consistency and independent of manufacturing tolerances, Fluid viscosity, and/or temperature variations, closed-loop control is used, and the internal fluid pressures 212 and 213 of the rotary or linear hydraulic actuating device 211 is sensed. In a closed hydraulic system, the actuator 211 will produce a high side pressure and a low side pressure on opposite sides of the rotary vane or piston when the control valve is operated to restrict the fluid flow. When the direction is reversed, the high and low side pressures are reversed. The sensed 212 and 213 pressures are signal conditioned and scaled to a usable analog level by circuitry 206. The processed analog hydraulic pressures are converted into a usable digital 8-16 bit valve by the microprocessor 200 or an external A/D converter. In the above mentioned applications, program state control logical branching into different sections of the main program as well as variations in calculations in the application dependent program 209 are accomplished by additional analog force sensors and/or digital switches or buttons 208 and 224 using auxiliary sensing In an exerciser or robotics application, the auxiliary sensing will be a user keypad and/or remote switches. In the knee control prosthesis application, the auxiliary sensing function uses two body weight sensors and two 16 position rotary selector switches.
The knee position sensor 216 is accomplished by a Honeywell linear Hall effect sensor 18 measuring the change in magnetic field with respect to the sensor. The magnet 14 is moved in reference to the sensor 18 or 216 in proportion to the knee angle of the prosthesis. The output of the sensor 216 is conditioned, offset, and scaled by the sensor circuitry 204. The microprocessor 200 converts this 0-5V analog level into an 8 bit digital value. The application program samples the position sensor at a 1000 times per second rate. The application program determines knee direction and course velocity information at that rate. Fine velocity is determined at the 100 times per second control rate. For variances between patients as to their size, weight, and gait characteristics, the prosthenst sets the flexion and extension rotary 16 position auxiliary switches 224. Other auxiliary circuits used for program state control are the two weight force sensors 220 and 221 being modulated, conditioned, demodulated, and scaled by circuitry 206. These weight force sensors are located in the bottom of the prosthesis (FIGS. 5 and 12A-D) to measure the force distribution applied during the gait cycle to determine when toe off, flat footed, and heel strike conditions exist along with their variations. This information is used in the adaptive closed-loop control algorithm with knee position, knee velocity, knee direction, and past gait learned characteristics to control the instantaneous resistance control over varying terrain.
Since this knee prosthesis is worn on the body, the control system is powered by 4 Lithium ion rechargeable batteries 218 or 19 yielding 14.4 volts. Power is split off into two circuit applied voltages being 7.2 volts for the system logic supply and raw 14.4 volts for the proportional control solenoid drive circuits. The raw voltage is monitored to detect a low battery condition by circuit 222 which scales the battery voltage into a 0-5 volt level to be read by the microprocessor 200 using its A/D converter. The microprocessor and associated logic circuits require 5V which is regulated from the 7.2 voltage input by the power circuits 203 which include a conventional low dropout three pin regulator integrated circuit. The Lithium ion batteries are recharged in a two hour period and then switched into a trickle charge mode by a LM3420-16.8 integrated circuit produced by National Semiconductor.
As the voltage from the digital pot is increased, the circuit applies a voltage across the solenoid coil. The current through the coil is in series with the sense resister 10 ohm R5. This constant current circuit increases or decreases the operational amplifiers output voltage until the voltage seen at the top of the sense resister is equal to the commanded voltage. Thus to require a 0 to 83 milliamp drive to the solenoid coil, a 0 to 4.9 volt input is required. The constant current circuit automatically compensates for coil resistance manufacturing variations and temperature effects.
This analog output is then converted into a digital output for use by the main program by the microprocessor 200.
In the knee control application (FIG. 17), two configurations of this sensor technology are illustrated. These are the hydraulic oil pressure sensors 206 and the body weight sensors 208.
In the knee control application (FIG. 17), the system software is written in assembly code for a Motorola MC68HC912B32 microprocessor 200. This microprocessor 200 includes a 16 bit CPU, an interrupt controller, an 8 channel 8 bit A/D converter, 1 kilobyte of RAM, 32 kilobytes of flash EPROM program memory, 756 bytes of EEPROM, one real-time timer interrupt, six timer-counters, a watchdog circuit, and a complex of communication devices for interacting with other systems such as a RS-232 serial peripheral, a synchronous serial peripheral, a BDLC synchronous serial peripheral, and a real-time background mode interface.
The knee control software application includes subroutines which are common to robotics and exercise devices. Referring to the general block diagram of
Referring to the knee control application software discussed above in connection with
The outer control loop feedback is obtained by the linear hall effect position sensor 216, such as the sensor 18, attached to the moveable knee joint housing 15. The analog output of the hall effect sensor 18 is non-linear. Part of the linearization is accomplished by the cam surface on the retainer plate 8 (FIG. 6). The majority of the position interpretation is accomplished by a software lookup table driver routine which converts raw position into actual knee angle in degrees and tenths. The raw position information is scaled and offset by the position sensor circuit 204 which is read by the microprocessor 200 using the A/D position driver software routine.
Two types of auxiliary program decision state control functions are used. One being analog and the other being digital. The analog program state sensors 220 and 221 form the dual body weight sensor 68 attached to the bottom on the knee control frame 5. The sensors 220 and 221 sense the amputee's weight being applied to the toe or flat footed, or heel force to aid the main software program control. The two sensors 220 and 221 also use the 100 kHz reference signal. The demodulated and scaled resultant analog signals are ready by the microprocessor 200 by A/D software drivers. Variations between the amputee's size, weight, age, strength are accommodated by the setting of ten levels of flexion and ten levels of extension profiles. These settings are made by the prosthetist during the knee control fitting. The main subminiature printed circuit card contains two sixteen position miniature rotary digital hexadecimal switches. The first ten positions are used for the prosthetic adjustments of flexion and extension and the other six are for special modes of operation tailored for sports and geriatrics. The two 4 bit auxiliary switch inputs 224 are read directly by the microprocessor using the switch software driver input routine and the I/O input pins and associated internal pull-up resisters. The input signals are normally seen as a digital high TTL level except when grounded by the switch.
Since this knee control application is battery powered, additional software low level drivers are required for this application. The battery pack 218, such as the battery pack 19, are conditioned and split into 5, 7.2, and 14.4 volts by the power circuits 203. The battery level is monitored by the microprocessor 200 through the conditioned battery sensed signal 222. The analog 0-5 volt filtered level is read by the microprocessor 200 by the low level software A/D battery driver routine. If the programs determine that the battery is within 30 minutes of a minimum safe level of operation, the two safety software routines will be activated to cause a vibrator circuit 227 to produce an alert to give the user impending notice of shutdown. The communication to the outside world to/from the knee control is through the microprocessor's internal communication ports and interface hardware circuitry 202. The asynchronous (SCI) and synchronous (SPI) serial data ports are used for special clinical data capture and control. The background mode (BDM) port is used for the factory test interface during the manufacturing process as well as during software development. The main programming of the 32 kilobytes flash memory is programmed through the BDM port.
The mainline program checks for low battery conditions and outside communications in the system idle time when not executing the interrupt driven adaptive closed-loop time dependent application. The mainline program examines two low level battery conditions; one being if the level is below 30 minutes of safe operation and the other if the battery is below 10 minutes of safe operating time left. The user is informed of the immediate loss of the system use from a low battery condition by either a vibration of one second on and 10 seconds off for the 30 minute case or one second on and one second off for the 10 minute case. In normal use, the Lithium Ion battery pack will last 22-30 hours before needing to be recharged. The knee control prosthetic will normally be recharged by the user every night. If needed, the user can charge the battery pack to 90 percent of its level in two hours while at work.
The new position is also subtracted from an old position of 50 milliseconds ago and divided by 50 milliseconds to calculate a long term knee velocity. The short term knee velocity is used for the determination of knee direction. The long term knee velocity is used for the determination of the knee resistance to be applied. The knee applied resistance calculations are based on the mathematical transfer function of a non-electronic hydraulic knee control obtained through extensive engineering characterization. A set of tables and equations are used to calculate the requires applied resistance in terms of PSI for any instantaneous knee position, knee velocity, knee direction, and flexion or extension patient switch setting. When the normal swing phase calculations are completed, the normal swing phase resistance is stored in the RAM for later use.
The program flow then determines if additional modes of operation are to be executed. The first decision path is Terminal Deceleration (T.D.). When the prosthetic knee is approaching full extension, the system software will apply an additional high resistance at less than 10 degrees to stop the knee hyper extending. Likewise, another routine is used for slowing the prosthetic knee during flexion. This is called Flexion Deceleration (F.D.). This routine is used to keep the knee from flexing too far. The F.D. routine will increase resistance proportionally past 65 degrees flexion and completely stops the knee control at 70 degrees. Other auxiliary modes include the determination of walking down stairs and the determination of stumbling. The down stairs mode is determined by knee angle and weight distribution as seen by the two weight force sensors 220 and 221. The electronic control extends the decaying stance mode of the mechanical portion of the control. If stumble recovery is required, it applies a high resistance to the knee control for a period of time and then delays it to zero. This mode attempts to protect the patient from falling and is detected by knee velocity, knee angle, and weight force distribution.
When the resistance software flow is complete, the desired force level to be applied is stored in a RAM variable. The application software will compute the best valve control level based on the knee velocity, knee direction, hydraulic characteristics, and valve characteristics. This level is written to a RAM variable location for use by the 1 millisecond interrupt routine previously mentioned.
The knee control application gait summary is shown in FIG. 21. The gait knee angle is shown by the curve 248. The swing phase is active when the knee control is off the ground with the knee bending in flexion or extension. Swing phase starts at toe off position 252 and is completed by the time the heel is just ready to strike at position 253. The electronic control is active anytime the knee is at any angle greater than zero except when it detects that the knee has stopped for more than 5 seconds. The stance phase consists of a heel strike position 249, full weight bearing load position 250, and almost toe off but still touching ground position 251.
The magnetic position sensor assembly 303 consists of a sensor housing enclosing a high output permanent magnet 304 (
The magnetic shutter position sensor assembly 303 generates a nonlinear output which is shown by the chart of FIG. 31. Through a software algorithm, the curve is divided into 13 equations representing 10 degrees of movement each which can be approximated by a series of straight line equations. This approach requires significantly less memory than a 12 bit 8192 byte lookup table which would require 25% of the imbedded microprocessor's program memory capacity. The sensor is calibrated by measuring the magnetic levels every 10 degrees over 0-130 degrees, the correct equation coefficients and stores these in the microcontroller's nonvolatile electrically erasable memory for use by the main executable application program.
The actuator housing 300 is constructed of aluminum and is sealed from leakage of the hydraulic fluid to the environment. The sensor electronic assembly 303 is similar to the position sensor electronic assembly 303 described above in reference to FIG. 25B and is mounted in a cavity outside of the sealed housing for sensing the internal magnetic field of the magnet 311 through the aluminum housing. The sensor card 305 is mounted on the housing with a screw 308. At zero hydraulic pressure, the air gap between the magnet and the GMR IC bridge sensor 306 is about 0.195 inch but increases to about 0.245 inch at 500 PSI differential pressure. As mentioned above, the common sensor card electronics contain the instrumentation amplifier 307 for signal conditioning. The signal level is transmitted to the microprocessor controller card using the cable assembly 309 for further signal conditioning and being converted to a usable digital value for use in the closed-loop control of the hydraulically applied resistance to the knee.
A patient weight bearing sensor mechanism (
The sensor remote assembly circuitry is shown on FIG. 29. The magnetic field is detected and measured by a Magnetoresistive GMR 5 kilo-ohm 100 oersted sensitivity bridge manufactured by Nonvolatile Electronics as part number AA005, and designated as UI. The bridge is excited by a precision 2.5 voltage reference. The same 2.5 volt reference is applied to a Burr-Brown INA122 designated as a U2 instrumentation micro-powered amplifier. The instrumentation amplifier uses a 14K gain resistor RG which converts the low level differential GMR bridge output into a 19.29 times increased level. The amplifier also conditions the signal to a low impedance drive level for transmitting to the main microprocessor control card in a low noise manner. Capacitor C1 is used as a power noise decoupler, and the output signal is at a level of 0-2.5 volts. The maximum magnet to sensor distance is selected to obtain a minimum amplifier output voltage of 1.25 volts thus transmitting the usable voltage range of 1.25V to 2.5V.
In place of the valve described above in
The pilot stage needle valve 332 is biased towards an open position by a spring 333 and controls fluid flowing through an orifice 326. The electromagnetic force acts mechanically through a steel armature 330 and is applied for closing the needle valve 332 for resisting flow, resulting in a proportional increase of pilot fluid pressure. This fluid pressure acts on the main poppet 320 to increase the system pressure. The main stage has two moving parts, the poppet valve 320 and a bias spring 324. The clearance between the poppet valve bore and its support spool is very small such as 0.0005 inch on the diameter in order to minimize pressure and flow losses due to leakage.
The forces acting on the main poppet valve 320 are relatively large but provide for smooth motion, low leakage and rapid response with a relative weak bias spring 324. The pilot stage has the moving parts of steel armature 330 and needle valve 332 and a compression spring 333. The armature 330 is mounted on a nonferrous or aluminum cylindrical pusher tube 331 that slides axially on a ground pin 329. The concentricity of these pieces with a bore in a flux plate 328 and a good surface finish between these pieces minimizes the friction of the pusher tube 331 and consequently minimize system hysterisis, helps repeatability and maximizes the efficiency of the magnetic system.
The pilot needle valve 332 moves relative to the pilot orifice 326 for reducing its effective flow area and resulting in an increase in pilot pressure. The smooth surface finish of the needle and the bore and the relatively close radial clearance between them minimize effects due to side loading from angular or radial misalignment of the needle and pusher tube 331. This helps reduce hysterisis and improves armature efficiency. The magnetic field is carried through a steel core 335, steel flux ring 336, steel case 338 and steel flux plate 328. These components are designed in accordance with dimensional requirements of the electromagnetic forces required for the system. A set of O-ring seals 325, 334 and 337 are used to keep the high pressure hydraulic fluid from leaking into the outside environment.
From the drawings and the above description, it is apparent that a device or apparatus constructed in accordance with the present invention, provides desirable features and advantages. For example, by sensing the differential pressure across the movable hydraulic actuator member and using this differential pressure in a computer controlled closed-loop system for the valve which controls the flow of hydraulic fluid to the actuator, a precisely controlled variable resistance is obtained regardless of variations in manufacturing tolerances, wear of parts, or variations in the viscosity of the hydraulic fluid. Thus apparatus constructed in accordance with the invention is ideally suited for producing a precise knee gait damping resistance for a knee prosthesis without returning by the patient or prosthetist.
As another advantage, the magnetic rotary or linear position sensor, pressure sensor and weight bearing sensor described in connection with
While the methods and forms of apparatus or devices herein described constitute preferred embodiments of the invention, it is to be understood that the invention is not limited to the precise methods and forms described, and that changes may be made therein without departing from the scope and spirit of the invention as defined in the appended claims.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3820168||Sep 11, 1972||Jun 28, 1974||Bock O Orthopaedische Ind Fa K||System for operating a prosthetic limb|
|US3995324||Sep 12, 1975||Dec 7, 1976||Actuator device for artificial leg|
|US4005496||Jun 13, 1975||Feb 1, 1977||Hosmer/Dorrance Corporation||Prosthetic knee joint|
|US4064569||Sep 23, 1976||Dec 27, 1977||Campbell Harry E||Artificial polycentric knee joint|
|US4065815||Sep 28, 1976||Jan 3, 1978||Sen Jung Chen||Hydraulically controlled artificial leg|
|US4209860||Feb 13, 1978||Jul 1, 1980||The United States of America as represented by the Administrator of Veterans' Affairs||System and method for multifunctional control of upper limb prosthesis via EMg signal identification|
|US4212087||Nov 16, 1978||Jul 15, 1980||Mortensen Lavaugh L||Prosthetic leg with a hydraulic control|
|US4310932||Sep 26, 1979||Jan 19, 1982||Naeder Max||Artificial knee-joint|
|US4354676||Oct 13, 1978||Oct 19, 1982||Pepsico, Inc.||Exerciser|
|US4569352||Nov 15, 1984||Feb 11, 1986||Wright State University||Feedback control system for walking|
|US4685927||May 28, 1986||Aug 11, 1987||Ott Bock Orthopaedische Industrie Besitz- und Verwaltungs-Komanditgesells chaft||Braked knee joint|
|US4711242||Feb 18, 1986||Dec 8, 1987||Wright State University||Control system for knee joint|
|US4711450||May 28, 1985||Dec 8, 1987||Mcarthur Jim||Multi-mode exercising apparatus|
|US4760850||May 15, 1986||Aug 2, 1988||Wright State University||Method for balancing assistance|
|US4790522||Feb 25, 1988||Dec 13, 1988||Trw Inc.||Electroviscous fluid control device|
|US4854428||Sep 22, 1988||Aug 8, 1989||Otto Bock Orthopadische Industrie Besitz- Und Verwaltungs-Kg||Double-acting hydraulic piston-and-cylinder device|
|US4876944||Mar 3, 1988||Oct 31, 1989||Duke University||Pneumatic limb control system|
|US4893648||Sep 30, 1988||Jan 16, 1990||Otto Bock Orthopadische Industrie Besitz - Und Verwaltungs - Kg||Control valve|
|US4919418||Apr 24, 1989||Apr 24, 1990||Miller Jan W||Computerized drive mechanism for exercise, physical therapy and rehabilitation|
|US4958705||Oct 28, 1988||Sep 25, 1990||Otto Bock Orthopadische Industrie Besitz-Und Verwaltungs - Kg||Hydraulic controller, especially for the movement of a prosthetic joint|
|US5062856||Mar 23, 1989||Nov 5, 1991||Kabushiki Kaisha Kobe Seiko Sho||Teaching playback swing-phase-controlled above-knee prosthesis|
|US5092902||Aug 9, 1991||Mar 3, 1992||Mauch Laboratories, Inc.||Hydraulic control unit for prosthetic leg|
|US5133774||Jun 3, 1991||Jul 28, 1992||Kabushiki Kaisha Kobe Seiko Sho||Teaching playback swing-phase-controlled above-knee prosthesis|
|US5181931||Jan 28, 1991||Jan 26, 1993||Otto Bock Orthopaedische Industrie Besitz- und Verwaltungs-Kommanditgesel lschaft||Swivel connection between two parts of an orthopedic technical aid|
|US5197488||Apr 5, 1991||Mar 30, 1993||N. K. Biotechnical Engineering Co.||Knee joint load measuring instrument and joint prosthesis|
|US5201772||Jan 31, 1991||Apr 13, 1993||Maxwell Scott M||System for resisting limb movement|
|US5230672||Mar 13, 1991||Jul 27, 1993||Motivator, Inc.||Computerized exercise, physical therapy, or rehabilitating apparatus with improved features|
|US5277281||Jun 18, 1992||Jan 11, 1994||Lord Corporation||Magnetorheological fluid dampers|
|US5284330||Jun 18, 1992||Feb 8, 1994||Lord Corporation||Magnetorheological fluid devices|
|US5336269||Jun 9, 1992||Aug 9, 1994||Liberty Mutual Insurance Co.||Method and apparatus for switching degrees of freedom in a prosthetic limb|
|US5383939||Dec 5, 1991||Jan 24, 1995||James; Kelvin B.||System for controlling artificial knee joint action in an above knee prosthesis|
|US5397287||Feb 6, 1991||Mar 14, 1995||Lindfors; Kai||Muscle exercising device|
|US5398917||Feb 7, 1994||Mar 21, 1995||Lord Corporation||Magnetorheological fluid devices|
|US5405409||Jan 21, 1994||Apr 11, 1995||Knoth; Donald E.||Hydraulic control unit for prosthetic leg|
|US5413611||Jul 21, 1992||May 9, 1995||Mcp Services, Inc.||Computerized electronic prosthesis apparatus and method|
|US5443521||Dec 30, 1993||Aug 22, 1995||Mauch Laboratories, Inc.||Hydraulic control unit for prosthetic leg|
|US5472412||Apr 5, 1994||Dec 5, 1995||Mauch Laboratories, Inc.||Limb brace with adjustable hydraulic resistance unit|
|US5476441||Sep 30, 1993||Dec 19, 1995||Massachusetts Institute Of Technology||Controlled-brake orthosis|
|US5545232||Feb 21, 1995||Aug 13, 1996||Otto Bock Orthopadische Industrie Besitz-und Verwaltungs-Kommanditgesesll schaft||Device for mutual pivoting connection of parts of an orthopaedic apparatus|
|US5571205||Nov 18, 1994||Nov 5, 1996||James; Kelvin B.||System for controlling artificial knee joint action in an above knee prosthesis|
|US5645590||May 31, 1995||Jul 8, 1997||Otto Rock Orthopadische Industrie Besitz-und Verwaltungs-Kommanditgesesll schaft||Pivot device between parts of an orthopedic aid|
|US5645752||Dec 20, 1995||Jul 8, 1997||Lord Corporation||Thixotropic magnetorheological materials|
|US5670077||Oct 18, 1995||Sep 23, 1997||Lord Corporation||Aqueous magnetorheological materials|
|US5683615||Jun 13, 1996||Nov 4, 1997||Lord Corporation||Magnetorheological fluid|
|US5704945||Feb 23, 1996||Jan 6, 1998||Otto Bock Orthopaedische Industrie Besitzund Verwaltungs-Kommanditgesells chaft||Brake-action knee joint|
|US5711746||Mar 11, 1996||Jan 27, 1998||Lord Corporation||Portable controllable fluid rehabilitation devices|
|US5728170||Sep 6, 1996||Mar 17, 1998||Otto Bock Orthopaedische Industrie Besitz- und Verwaltungs-Kommanditgesel lschaft||Below-knee prosthesis|
|US5728174||Mar 30, 1995||Mar 17, 1998||Biedermann Motech Gmbh||Swing phase control for an artificial knee joint|
|US5746774||Jan 16, 1996||May 5, 1998||The University Of Toledo||Knee joint mechanism for knee disarticulation prosthesis|
|US5749533||Aug 3, 1995||May 12, 1998||Daniels; John J.||Fishing reel with electronically variable brake for preventing backlash|
|US5755813||Mar 28, 1996||May 26, 1998||Otto Bock Orthopaedische Industrie Besitz-Und Verwaltungs-Kommanditgesell Schaft||Prosthetic brake joint|
|US5823309||May 23, 1997||Oct 20, 1998||General Motors Corporation||Magnetorheological transmission clutch|
|US5842547||Jul 2, 1996||Dec 1, 1998||Lord Corporation||Controllable brake|
|US5888212||Jun 26, 1997||Mar 30, 1999||Mauch, Inc.||Computer controlled hydraulic resistance device for a prosthesis and other apparatus|
|US5888236||Jan 22, 1997||Mar 30, 1999||Otto Bock Orthopadische Industrie Besitz Und Verwaltungs Kommanditgesellschaft||Pivot device between parts of an orthopedic aid|
|US5893891||Jul 14, 1997||Apr 13, 1999||Chas. A. Blatchford & Sons Limited||Prosthesis control system|
|US5900184||Oct 18, 1995||May 4, 1999||Lord Corporation||Method and magnetorheological fluid formulations for increasing the output of a magnetorheological fluid device|
|US5906767||Oct 28, 1997||May 25, 1999||Lord Corporation||Magnetorheological fluid|
|US5947238||Mar 5, 1997||Sep 7, 1999||Lord Corporation||Passive magnetorheological fluid device with excursion dependent characteristic|
|US5948021||Feb 24, 1998||Sep 7, 1999||Hosmer-Dorrance Corporation||Hydraulic cylinders for limb gait control|
|US5960918||Mar 27, 1998||Oct 5, 1999||Behr America, Inc.||Viscous clutch assembly|
|US5967273||Oct 17, 1997||Oct 19, 1999||Eaton Corporation||Magneto-rheological fluid coupling|
|US6027664||Aug 12, 1998||Feb 22, 2000||Lord Corporation||Method and magnetorheological fluid formulations for increasing the output of a magnetorheological fluid|
|US6095486||Mar 5, 1997||Aug 1, 2000||Lord Corporation||Two-way magnetorheological fluid valve assembly and devices utilizing same|
|US6113642||Nov 10, 1998||Sep 5, 2000||Mauch, Inc.||Computer controlled hydraulic resistance device for a prosthesis and other apparatus|
|US6117177||Mar 12, 1999||Sep 12, 2000||Teh Lin Prosthetic & Orthopaedic Inc.||Artificial knee joint having a swing phase control member|
|US6139586||Mar 11, 1999||Oct 31, 2000||Otto Bock Orthopaedische Industrie Besitz- und Verwaltungs-Kommanditgesel lschaft||Prosthesis brake joint|
|US6168634||Mar 25, 1999||Jan 2, 2001||Geoffrey W. Schmitz||Hydraulically energized magnetorheological replicant muscle tissue and a system and a method for using and controlling same|
|US6352144||Nov 18, 1997||Mar 5, 2002||Advanced Fluid Systems Limited||Flow-control valve and damper|
|US6423098||Dec 10, 1998||Jul 23, 2002||Biedermann Motech Gmbh||Leg prosthesis with an artificial knee joint provided with an adjustment device|
|US6443993||Mar 23, 2001||Sep 3, 2002||Wayne Koniuk||Self-adjusting prosthetic ankle apparatus|
|US6517585||Aug 13, 1998||Feb 11, 2003||Chas. A. Blatchford & Sons Limited||Lower limb prosthesis|
|US6679920||Jan 5, 2001||Jan 20, 2004||Biedermann Motech Gmbh||Device and method for remote maintenance of an electronically controllable prosthesis|
|US6695885||Nov 15, 2001||Feb 24, 2004||Alfred E. Mann Foundation For Scientific Research||Method and apparatus for coupling an implantable stimulator/sensor to a prosthetic device|
|US6719806||Mar 3, 1999||Apr 13, 2004||Chas. A. Blatchford & Sons Limited||Lower limb prosthesis and control unit|
|US6764520||Jan 22, 2001||Jul 20, 2004||Massachusetts Institute Of Technology||Electronically controlled prosthetic knee|
|USRE36521||Oct 15, 1996||Jan 18, 2000||Otto Bock Orthopaedische Industrie Besitz - Und Verwaltungs Kg||Connecting part between leg prosthesis components|
|DE3543291A1||Dec 7, 1985||Jun 11, 1987||Bosch Gmbh Robert||Hydraulic shock absorber (damper)|
|DE4229330A1||Sep 2, 1992||Mar 10, 1994||Ludger Springob||Limb function restoration using somatronic device - has microchip which responds to detected movement of sound limb to provide signals for stimulating impaired limb|
|EP0503775A1||Feb 17, 1992||Sep 16, 1992||CHAS. A. BLATCHFORD & SONS LIMITED||An artificial leg|
|EP0549855A2||Sep 12, 1992||Jul 7, 1993||Otto Bock Orthopädische Industrie Besitz- und Verwaltungs-Kommanditgesellschaft||System for controlling artificial knee joint action in an above knee prosthesis|
|EP0628296A2||May 27, 1994||Dec 14, 1994||CHAS. A. BLATCHFORD & SONS LIMITED||Prosthesis control system|
|EP1125825A2||Jan 17, 2001||Aug 22, 2001||Delphi Technologies, Inc.||Variable road feedback device for steer-by-wire systems|
|FR2623086A1||Title not available|
|GB2201260A||Title not available|
|GB2244006A||Title not available|
|GB2268070A||Title not available|
|GB2328160A||Title not available|
|GB2334891A||Title not available|
|GB2338653A||Title not available|
|JPH0478337A||Title not available|
|JPH03181633A||Title not available|
|JPS6081530A||Title not available|
|WO1996041599A1||Jun 6, 1996||Dec 27, 1996||Otto Bock Orthopädische Industrie Besitz- Und Verwaltungskommanditgesellschaft||Process for controlling the knee brake of a knee prosthesis and thigh prosthesis|
|WO1999008621A2||Aug 13, 1998||Feb 25, 1999||Chas. A. Blatchford & Sons Limited||A lower limb prosthesis|
|WO1999029272A1||Dec 10, 1998||Jun 17, 1999||Biedermann Motech Gmbh||Leg prosthesis with an artificial knee joint provided with an adjustment device|
|WO2002080825A2||Mar 30, 2002||Oct 17, 2002||Otto Bock Austria Ges.M.B.H.||Device for pivotably connecting parts of an orthopaedic device|
|1||"Design Principles, Biomedical Data and Clinical Experience with a Polycentric Knee Offering Controlled Stance Phase Knee Flexion: A Preliminary Report", Siegmar Blumentritt, Ph. D. et al 1997, Journal of Prosthetics and Orthotics, vol. 9, No. 1, 18-24.|
|2||"Optimal Control For An Above-Knee Prosthesis With Two Degrees Of Freedom", D. Popovic et al, 1995, pp. 89-98, J. Biomechanics, vol. 28, No. 1.|
|3||An Auto-Adaptive External Knee Prosthesis, Ari Wilkenfeld & Hugh Herr, Artificial Intelligence Laboratory, MIT, Cambridge, Massachusetts, 3 pages, Sep. 2000.|
|4||Biologically inspired autoadaptive control of a knee prosthesis, Air Wilkenfeld, Ph. D., Dissertation Abstract, MIT, Cambridge, Massachusetts, 1 page, Sep. 2000.|
|5||Otto Bock Orthopadische Industrie, C-LEG A new dimension in amputee mobility, Otto Bock 1997 (4 pages).|
|6||State-Of-The-Art Prosthetic Leg Incorporates Magneto-Rheological Technology, Medical Product Manufacturing News, p. 42, Nov. 2000.|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7652386 *||Apr 30, 2008||Jan 26, 2010||Bionic Power Inc.||Method and apparatus for harvesting biomechanical energy|
|US7659636||Feb 9, 2010||Bionic Power Inc.||Methods and apparatus for harvesting biomechanical energy|
|US7799091||Oct 8, 2007||Sep 21, 2010||Massachusetts Institute Of Technology||Control system for prosthetic knee|
|US8287477||Feb 1, 2012||Oct 16, 2012||Massachusetts Institute Of Technology||Active ankle foot orthosis|
|US8299634||Aug 10, 2006||Oct 30, 2012||Bionic Power Inc.||Methods and apparatus for harvesting biomechanical energy|
|US8376971||Feb 19, 2013||Massachusetts Institute Of Technology||Active ankle foot orthosis|
|US8419804||Sep 1, 2009||Apr 16, 2013||Iwalk, Inc.||Hybrid terrain-adaptive lower-extremity systems|
|US8487456||Oct 10, 2012||Jul 16, 2013||Bionic Power Inc.||Methods and apparatus for harvesting biomechanical energy|
|US8500823||Feb 1, 2010||Aug 6, 2013||Massachusetts Institute Of Technology||Powered artificial knee with agonist-antagonist actuation|
|US8512415||Jun 12, 2008||Aug 20, 2013||Massachusetts Institute Of Technology||Powered ankle-foot prothesis|
|US8551029||Feb 13, 2013||Oct 8, 2013||Massachusetts Institute Of Technology||Active ankle foot orthosis|
|US8551184||Feb 1, 2012||Oct 8, 2013||Iwalk, Inc.||Variable mechanical-impedance artificial legs|
|US8698329||May 25, 2012||Apr 15, 2014||Kcf Technologies, Inc.||Apparatuses and methods for using energy harvesting for variable shock absorption in a prosthetic device|
|US8734528||Dec 21, 2012||May 27, 2014||Massachusetts Institute Of Technology||Artificial ankle-foot system with spring, variable-damping, and series-elastic actuator components|
|US8736087||Sep 1, 2011||May 27, 2014||Bionic Power Inc.||Methods and apparatus for control of biomechanical energy harvesting|
|US8801803||Nov 30, 2009||Aug 12, 2014||Korea Workers' Compensation & Welfare Service||Connection structure of artificial limb and socket, using magnetic locking device|
|US8808214||Nov 18, 2011||Aug 19, 2014||Massachusetts Institute Of Technology||Active ankle foot orthosis|
|US8864846||Feb 1, 2010||Oct 21, 2014||Massachusetts Institute Of Technology||Model-based neuromechanical controller for a robotic leg|
|US8870967||Oct 29, 2009||Oct 28, 2014||Massachusetts Institute Of Technology||Artificial joints using agonist-antagonist actuators|
|US8900325||Sep 24, 2013||Dec 2, 2014||Iwalk, Inc.||Hybrid terrain-adaptive lower-extremity systems|
|US8926711||Mar 4, 2013||Jan 6, 2015||College Park Industries, Inc.||Prosthetics using curved dampening cylinders|
|US8928161||May 25, 2012||Jan 6, 2015||Kcf Technologies, Inc.||Apparatuses and methods for harvesting energy from prosthetic limbs|
|US9028557||Mar 14, 2013||May 12, 2015||Freedom Innovations, Llc||Prosthetic with voice coil valve|
|US9032635||Dec 14, 2012||May 19, 2015||Massachusetts Institute Of Technology||Physiological measurement device or wearable device interface simulator and method of use|
|US9057361||Jun 27, 2013||Jun 16, 2015||Bionic Power Inc.||Methods and apparatus for harvesting biomechanical energy|
|US9060883||Mar 12, 2012||Jun 23, 2015||Iwalk, Inc.||Biomimetic joint actuators|
|US9149370||Aug 5, 2013||Oct 6, 2015||Massachusetts Institute Of Technology||Powered artificial knee with agonist-antagonist actuation|
|US9194403 *||Feb 23, 2014||Nov 24, 2015||Dylan Pierre Neyme||Modular hinged joint for use with agonist-antagonist tensile inputs|
|US9211201||Mar 15, 2013||Dec 15, 2015||Iwalk, Inc.||Hybrid terrain-adaptive lower-extremity systems|
|US9221177||Apr 18, 2013||Dec 29, 2015||Massachusetts Institute Of Technology||Neuromuscular model-based sensing and control paradigm for a robotic leg|
|US9222468||Apr 30, 2014||Dec 29, 2015||Bionic Power Inc.||Methods and apparatus for control of biomechanical energy harvesting|
|US9333097||Jun 28, 2011||May 10, 2016||Massachusetts Institute Of Technology||Artificial human limbs and joints employing actuators, springs, and variable-damper elements|
|US9339397||May 21, 2014||May 17, 2016||Massachusetts Institute Of Technology||Artificial ankle-foot system with spring, variable-damping, and series-elastic actuator components|
|US9345592||Sep 1, 2009||May 24, 2016||Bionx Medical Technologies, Inc.||Hybrid terrain-adaptive lower-extremity systems|
|US9351856||Sep 24, 2013||May 31, 2016||Iwalk, Inc.||Hybrid terrain-adaptive lower-extremity systems|
|US20110112447 *||Oct 5, 2010||May 12, 2011||The Board Of Trustees Of The University Of Illinois||Portable active fluid powered ankle-foot orthosis|
|US20150240842 *||Feb 23, 2014||Aug 27, 2015||Dylan Pierre Neyme||Modular hinged joint for use with agonist-antagonist tensile inputs|
|EP2778436A1||Jan 22, 2014||Sep 17, 2014||Freedom Innovations, LLC||Prosthetic with voice coil valve|
|WO2011057794A1||Nov 12, 2010||May 19, 2011||Otto Bock Healthcare Products Gmbh||Method and device for controlling an artificial orthotic or prosthetic joint|
|WO2011065608A1 *||Nov 30, 2009||Jun 3, 2011||Korea Workers Accident Medical Center||Connection structure of artificial limb and socket, using magnetic locking device|
|U.S. Classification||623/24, 623/44, 188/282.3|
|International Classification||F16F9/46, A61F2/50, A61F2/64, F16F9/44, A61F2/60, A61F2/70, A61F2/76, A61F2/68, A61F2/74|
|Cooperative Classification||A61F2/68, A61F2002/7635, A61F2/64, A61F2002/745, A61F2002/5007, A61F2002/704, A61F2002/7625, A61F2002/748, A61F2002/7655, A61F2002/5006, A61F2002/5072, F16F9/46, A61F2002/5032, F16F9/464|
|European Classification||F16F9/46, A61F2/68, F16F9/46P|