U.S. patent application number 14/733757 was filed with the patent office on 2015-09-24 for systems and methods for processing limb motion.
The applicant listed for this patent is Ossur hf. Invention is credited to Arinbjorn Viggo Clausen, Helgi Jonsson, Heidrun G. Ragnarsdottir.
Application Number | 20150265429 14/733757 |
Document ID | / |
Family ID | 36143417 |
Filed Date | 2015-09-24 |
United States Patent
Application |
20150265429 |
Kind Code |
A1 |
Jonsson; Helgi ; et
al. |
September 24, 2015 |
SYSTEMS AND METHODS FOR PROCESSING LIMB MOTION
Abstract
Control systems and methods are disclosed for processing a time
series of signals associated with the movement of a device
associated with a limb. The time series of motion signals is
filtered, such as thorough an autoregressive filter, and compared
to stored data sets representing a limb-motion event and/or phase.
In certain examples, a plurality of accelerometers generate the
time series of motion signals based at least on acceleration
measurements in three orthogonal directions and/or planes. The
acceleration measurements may relate to the movement of an
artificial limb, such as a prosthetic or orthotic device. Upon
determining an event and/or phase of limb motion, the control
system may trigger an actuator to appropriately adjust one or more
prosthetic or orthotic joints.
Inventors: |
Jonsson; Helgi; (Reykjavik,
IS) ; Clausen; Arinbjorn Viggo; (Reykjavik, IS)
; Ragnarsdottir; Heidrun G.; (Reykjavik, IS) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
Ossur hf |
Reykjavik |
|
IS |
|
|
Family ID: |
36143417 |
Appl. No.: |
14/733757 |
Filed: |
June 8, 2015 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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12855306 |
Aug 12, 2010 |
9078774 |
|
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14733757 |
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11315648 |
Dec 22, 2005 |
7811333 |
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12855306 |
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60638802 |
Dec 22, 2004 |
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Current U.S.
Class: |
623/25 |
Current CPC
Class: |
A61F 2002/7665 20130101;
A61F 2/72 20130101; A61F 2002/764 20130101; A61F 2002/6657
20130101; A61B 5/112 20130101; A61F 2002/763 20130101; A61F
2002/607 20130101; A61F 2002/7635 20130101; A61F 2002/6614
20130101; A61F 2002/704 20130101; A61F 2002/701 20130101; A61F
2002/7685 20130101; A61F 2/68 20130101; G01C 21/16 20130101; A61F
2/6607 20130101; A61F 2/70 20130101; A61B 5/4851 20130101 |
International
Class: |
A61F 2/72 20060101
A61F002/72; A61F 2/70 20060101 A61F002/70 |
Claims
1-30. (canceled)
31. A system comprising: an actuatable prosthetic device being
moveable about a joint; at least one sensor; a control system
comprising a processor and memory, the control system
communicatively coupled to the at least one sensor and configured
to: receive a time series of motion signals indicative of a
movement of the prosthetic device, filter at least one time series
of motion signal of the time series of motion signals, process the
filtered at least one time series of motion signal to identify at
least one limb-motion category, and cause an actuator to control
movement of the actuatable prosthetic device based at least in part
on the identified at least one limb-motion category.
32. The system of claim 31, wherein the at least one sensor
comprises a myoelectric sensor.
33. The system of claim 31, wherein the at least one sensor
comprises at least one of an accelerometer and a gyroscope.
34. The system of claim 31, wherein the limb-motion category
comprises at least one of level ground walking, walking up or down
stairs, walking up or down ramps, running, inclination,
declination, step, and non-step.
35. The system of claim 31, wherein the memory is configured to
store at least one of data associated with the received time series
signal, experimental data, or calibration data.
36. The system of claim 31, further comprising an interface for
communication with a user or an external device.
37. The system of claim 31, wherein, to process the filtered at
least one time series of motion signal to identify at least one
limb-motion category, the control system is configured to compare
the filtered at least one time series of motion signal with a set
of sample time series of motion signals.
38. The system of claim 31, wherein the control system is further
configured to identify at least one of heel strike, toe down, heel
off, toe off, midswing or end of swing.
39. A method of controlling operation of an actuatable prosthetic
device being moveable about a joint, the method comprising:
producing, using at least one sensor, a time series of motion
signals indicative of a movement of the actuatable prosthetic
device; receiving at a processor the time series of motion signals
indicative of the movement of the prosthetic device; filtering,
using said processor, selected at least one time series of motion
signal of the time series of motion signals; processing, using said
processor, the filtered at least one time series of motion signal
to identify at least one limb-motion category; and causing an
actuator to control movement of the actuatable prosthetic device
based at least in part on the identified at least one limb-motion
category.
40. The method of claim 39, wherein the at least one sensor
comprises a myoelectric sensor.
41. The method of claim 39, wherein the at least one sensor
comprises at least one of an accelerometer and a gyroscope.
42. The method of claim 39, wherein the limb-motion category
comprises at least one of level ground walking, walking up or down
stairs, walking up or down ramps, running, inclination,
declination, step, and non-step.
43. The method of claim 39, further comprising storing data
associated with at least one of the time series of motion signals,
experimental data, or calibration data.
44. The method of claim 39, further comprising communicating with a
user or an external device through an interface.
45. The method of claim 39, wherein said processing the filtered at
least one time series of motion signal comprises comparing the
filtered at least one time series of motion signal with a set of
sample series of motion signals to identify the at least one
limb-motion category.
46. The method of claim 39, further comprising identifying at least
one of heel strike, toe down, heel off, toe off, midswing and end
of swing.
47. A system comprising: a means for producing a time series of
motion signals indicative of a movement of an actuatable prosthetic
device; a means for receiving the time series of motion signals
indicative of the movement of the actuatable prosthetic device; a
means for filtering selected at least one time series of motion
signal of the time series of motion signals; a means for processing
the filtered at least one time series of motion signal to identify
at least one limb-motion category; and a means for controlling
movement of the actuatable prosthetic device based at least in part
on the identified at least one limb-motion category.
48. The system of claim 47, wherein the means for producing a time
series of motion signals indicative of a movement of an actuatable
prosthetic device comprises a myoelectric sensor.
49. The system of claim 47, further comprising a means for
identifying at least one limb-motion event comprising at least one
of heel strike, toe down, heel off, toe off, midswing and end of
swing.
50. The system of claim 47, wherein the at least one limb-motion
category comprises at least one of level ground walking, walking up
or down stairs, walking up or down ramps, running, inclination,
declination, step, and non-step.
Description
INCORPORATION BY REFERENCE TO ANY PRIORITY APPLICATIONS
[0001] Any and all applications, for which a foreign or domestic
priority claim is identified in the Application Data Sheet as filed
with the present application, are hereby incorporated by reference.
For example, this application is a continuation of U.S. patent
application Ser. No. 12/855,306, filed on Aug. 12, 2010, entitled
"SYSTEMS AND METHODS FOR PROCESSING LIMB MOTION," which is a
divisional of U.S. patent application Ser. No. 11/315,648, filed on
Dec. 22, 2005, now U.S. Pat. No. 7,811,333, entitled "SYSTEMS AND
METHODS FOR PROCESSING LIMB MOTION," which claims the benefit of
priority under 35 U.S.C. .sctn.119(e) of U.S. Provisional
Application No. 60/638,802, filed on Dec. 22, 2004, and entitled
"SYSTEMS AND METHODS FOR GAIT DETECTION," the entirety of each of
which is hereby incorporated herein by reference to be considered a
part of this specification.
BACKGROUND
[0002] 1. Field
[0003] Embodiments of the invention described herein relate
generally to limb-motion detection and, in particular, limb-motion
detection using a plurality of sensor signals.
[0004] 2. Description of the Related Art
[0005] Millions of individuals worldwide rely on prosthetic and/or
orthotic devices to compensate for disabilities, such as amputation
or debilitation, and to assist in the rehabilitation of injured
limbs. Orthotic devices include external apparatuses used to
support, align, prevent, protect, correct deformities of, or
improve the function of movable parts of the body. Prosthetic
devices include apparatuses used as artificial substitutes for a
missing body part, such as an arm or leg.
[0006] Conventional orthoses are often used to support a joint,
such as an ankle or a knee, of an individual, and movement of the
orthosis is generally based solely on the energy expenditure of the
user. Some conventional prostheses are equipped with basic
controllers that artificially mobilize the joints without any
interaction from the amputee and are capable of generating only
basic motions. Such basic controllers do not take into
consideration the dynamic conditions of the working environment.
The passive nature of these conventional prosthetic and orthotic
devices typically leads to movement instability, high energy
expenditure on the part of the disabled person or amputee, gait
deviations and other short- and long-term negative effects. This is
especially true for leg orthoses and prostheses.
[0007] To address these drawbacks, some prosthetic devices include
one or more systems for monitoring the movement of a user. For
instance, certain prosthetic knee devices include one or more
pressure sensors implanted in an insole for detecting changes in
force during user movement. In response to these detected changes
in force, a control unit mechanically adjusts the prosthetic knee.
Such measurements, however, are generally usable only for analysis
of the past gait of the user. Furthermore, because the pressure
sensors are generally used to detect contact between the foot and
the ground, the pressure sensors are not able to produce usable
signals during a swing stage of the foot. In addition, the insole
containing the pressure sensors often requires precise placement
and alignment in relation to the limb being monitored.
SUMMARY
[0008] Accordingly, a need exists for improved systems and methods
for detecting and analyzing movement of a device associated with a
limb. In particular, a need exists for systems and methods for
accurately detecting and/or predicting motion-related events and
phases, such as by processing a discrete and/or continuous signal
representing a stride of a user during a stance stage and a swing
stage. What are also needed are systems for controlling the
movement of a device associated with a limb based on the monitored
motion of the device.
[0009] In certain embodiments, a system is disclosed for analyzing
the movement of a device associated with a limb. The system
comprises at least one accelerometer configured to generate a time
series of motion signals indicative of a movement of a device
associated with a limb. The system further comprises a process
module in communication with the at least one accelerometer, the
process module comprising a filter and a comparison module. The
filter is configured to process the time series of motion signals
received from the at least one accelerometer and configured to
generate a plurality of filtered signals. The comparison module is
configured to compare the plurality of filtered signals with a
plurality of sample signals, wherein the comparison module is
further configured to identify limb-motion events associated with
the movement of the device associated with the limb. In certain
further embodiments, the system is incorporated into an actuatable
prosthetic or orthotic device being movable about a joint, such as,
for example, an ankle joint.
[0010] In certain embodiments, a method is disclosed for processing
signals associated with the movement of a device associated with a
limb. The method comprises receiving a time series of motion
signals indicative of movement of a device associated with a limb
and filtering selected ones of the time series of motion signals.
The method further includes processing the filtered signals to
identify at least one limb-motion category.
[0011] In certain embodiments, a method is disclosed for processing
signals associated with the movement of a device associated with a
limb. The method includes receiving a plurality of sensor signals
indicative of a motion of a device associated with a limb. The
method further includes processing the plurality of sensor signals
with a time series analysis and comparing the processed sensor
signals to a plurality of motion patterns so as to associate the
processed sensor signals with a particular motion pattern.
[0012] In certain embodiments, a system is disclosed for processing
signals associated with the movement of a device associated with a
limb. The system includes means for receiving a time series of
motion signals indicative of movement of a device associated with a
limb. The system further includes means for filtering selected ones
of the time series of motion signals and means for processing the
filtered signals to identify at least one limb-motion category.
[0013] In certain embodiments of the invention, a system is
disclosed for processing signals associated with the movement of a
prosthetic ankle device. The system includes means for receiving a
plurality of sensor signals indicative of a motion of a device
associated with a limb. The system further includes means for
processing the plurality of sensor signals with a time series
analysis and means for comparing the processed sensor signals to a
plurality of motion patterns so as to associate the processed
sensor signals with a particular motion pattern.
[0014] Another embodiment of the invention includes a machine
loadable software program for a processor for controlling the
movement of a device associated with a limb. The software program
includes an input module, a filter module, a comparison module, and
a control module. The input module is configured to receive a time
series of motion signals. The filter module is configured to
process the time series of motion signals and is configured to
generate a plurality of filtered signals. The comparison module is
configured to compare the plurality of filtered signals with a
plurality of sample signals and configured to generate a gait event
selection signal indicative of the movement of a device associated
with a limb. The control module is configured to generate a control
signal based at least in part on the gait event selection signal,
wherein the control signal is capable of causing the movement of
the device associated with the limb. The software module may
include, for example, an autoregressive (AR) filter and/or a Kalman
filter. The time series of motion signals may be indicative of
acceleration in at least one direction of the device associated
with the limb.
[0015] For purposes of summarizing the invention, certain aspects,
advantages and novel features of the invention have been described
herein. It is to be understood that not necessarily all such
advantages may be achieved in accordance with any particular
embodiment of the invention. Thus, the invention may be embodied or
carried out in a manner that achieves or optimizes one advantage or
group of advantages as taught herein without necessarily achieving
other advantages as may be taught or suggested herein.
BRIEF DESCRIPTION OF THE DRAWINGS
[0016] FIG. 1 illustrates a block diagram of a system architecture
of a control system for a prosthetic/orthotic device according to
certain embodiments of the invention.
[0017] FIGS. 2A and 2B illustrate exemplary data detection sets
relating to level ground walking by a user.
[0018] FIG. 3 illustrates a flowchart of an exemplary embodiment of
a gait stride detection process executable by the control system of
FIG. 1.
[0019] FIG. 4 illustrates a flowchart of an exemplary embodiment of
an event detection process executable by the control system of FIG.
1.
[0020] FIGS. 5A and 5B illustrate a dataflow diagram of an
exemplary embodiment of a data comparison process executable by the
control system of FIG. 1.
[0021] FIG. 6 illustrates a perspective view of an exemplary
embodiment of a lower-limb prosthesis usable with the control
system of FIG. 1.
DETAILED DESCRIPTION
[0022] Embodiments of the invention disclosed herein relate
generally to limb-motion detection, and in particular, to
determining the gait of a user to control, such as in real time, an
actuatable prosthetic or orthotic device. In certain embodiments,
the invention is used to identify a gait pattern of a user, a gait
state and/or a terrain on which the user is traveling. While the
description sets forth various embodiment-specific details, it will
be appreciated that the description is illustrative only and should
not be construed in any way as limiting the invention. Furthermore,
various applications of the invention, and modifications thereto,
which may occur to those who are skilled in the art, are also
encompassed by the general concepts described herein.
[0023] The features of the system and method will now be described
with reference to the drawings summarized above. Throughout the
drawings, reference numbers are reused to indicate correspondence
between referenced elements. The drawings, associated descriptions,
and specific implementation are provided to illustrate embodiments
of the invention and not to limit the scope of the disclosure.
[0024] Moreover, methods and functions described herein are not
limited to any particular sequence, and the acts or blocks relating
thereto can be performed in other sequences that are appropriate.
For example, described acts or blocks may be performed in an order
other than that specifically disclosed, or multiple acts or blocks
may be combined in a single act or block.
[0025] The terms "prosthetic" and "prosthesis" as used herein are
broad terms and are used in their ordinary sense and refer to,
without limitation, any system, device or apparatus usable as an
artificial substitute or support for a body part.
[0026] The term "orthotic" and "orthosis" as used herein are broad
terms and are used in their ordinary sense and refer to, without
limitation, any system, device or apparatus usable to support,
align, prevent, protect, correct deformities of, immobilize, or
improve the function of parts of the body, such as joints and/or
limbs.
[0027] The term "coronal" as used herein is a broad term and is
used in its ordinary sense and relates to any description,
location, or direction relating to, situated in, or being in or
near the plane that passes through the long axis of the body. A
"coronal plane" may also refer to any plane that passes vertically
or approximately vertically through the body and is perpendicular
or approximately perpendicular to the median plane and that divides
the body into anterior and posterior sections.
[0028] The term "sagittal" as used herein is a broad term and is
used in its ordinary sense and relates to any description,
location, or direction relating to, situated in, or being in or
near the median plane (i.e., the plane divides the body lengthwise
into right and left halves) or any plane parallel or approximately
parallel thereto. A "sagittal plane" may also refer to any vertical
anterior to posterior plane that passes through the body parallel
or approximately parallel to the median plane and that divides the
body into equal or unequal right and left sections.
[0029] The term "transverse" as used herein with respect to
physiology is a broad term and is used in its ordinary sense and
relates to any description, location, or direction relating to,
situated in, or being in or near a plane that divides the body into
top and bottom portions or any plane parallel or approximately
parallel thereto. A "transverse plane" may also refer to any
horizontal or substantially horizontal plane that divides the body
into equal or unequal top and bottom sections.
[0030] The term "time series" as used herein is a broad term and is
used in its ordinary sense and includes, without limitation, a
plurality of data points spaced apart at uniform or substantially
uniform time intervals. Such data points may be in a continuous
(with either a uniform or a non-uniform sampling rate) and/or a
sequential (discrete) form. A "time series analysis" comprises a
method for processing a time series of signals to determine
patterns of trend and/or forecast (predict) one or more values.
[0031] The terms "limb-motion event" and "gait event" as used
herein are broad terms and are used in their ordinary sense and
relate to, without limitation, distinct positions of a limb during
movement, such as during a gait cycle. For example, a gait event
for a stride of an individual may include toe off, heel strike,
midswing, or the like.
[0032] The terms "limb-motion phase," "gait phase," "limb-motion
category" and "gait category" as used herein are broad terms and
are used in their ordinary sense and relate to, without limitation,
forms or categories of limb movement. For example, a gait phase for
a stride may include level ground walking, walking up or down
stairs, walking up or down ramps, running and the like.
[0033] FIG. 1 illustrates a block diagram of one embodiment of a
system architecture of a control system 100 for a
prosthetic/orthotic device. In certain embodiments, the control
system 100 is usable with a lower limb prosthesis, such as, for
example, an ankle-motion controlled prosthetic device described in
copending U.S. application Ser. No. 11/056,344, filed Feb. 11,
2005, entitled "SYSTEM AND METHOD FOR MOTION-CONTROLLED FOOT UNIT,"
and published on Sep. 8, 2005, as U.S. Patent Publication No.
20050197717A1, which is hereby incorporated herein by reference in
its entirety to be considered a part of this specification. In
other embodiments, the control system 100 is usable by an orthotic
system or a rehabilitation system having a motion-controlled foot
or other motion-controlled limb.
[0034] As depicted in FIG. 1, the control system 100 includes a
sensor module 102, a processor 104, a memory 106, an interface 108,
a control drive module 110, an actuator 112 and a power module 114.
In certain embodiments, the control system 100 processes data
received from the sensor module 102 with the processor 104. The
processor 104 communicates with the control drive module 110 to
control the operation of the actuator 112 to mimic natural joint
movement (e.g., by adjusting the prosthetic/orthotic device).
Furthermore, the control system 100 may predict how the
prosthetic/orthotic device may need to be adjusted in order to
accommodate movement by the user. The processor 104 may also
receive commands from a user and/or other device through the
interface 108. The power module 114 provides power to the other
components of the control system 100.
[0035] FIG. 1 illustrates the sensor module 102 communicating with
the processor 104. In certain embodiments, the sensor module 102
advantageously provides measurement data to the processor 104
and/or to other components of the control system 100. For example,
the sensor module 102 may be coupled to a transmitter, such as, for
example, a BLUETOOTH.RTM. transmitter, that sends the sensed
measurements to the processor 104. In other embodiments, other
types of transmitters or wireless technology may be used, such as
infrared, WIFI.RTM., or radio frequency (RF) technology. In other
embodiments, wired technologies may be used to communicate with the
processor 104.
[0036] In certain embodiments, the sensor module 102 measures
variables relating to the prosthetic/orthotic device, such as the
position and/or the movement of the prosthetic/orthotic device
during one or more portions of a gait cycle. For instance, the
sensor module 102 may be advantageously located on the pro
sthetic/orthotic device, such as near a mechanical ankle center of
rotation.
[0037] In other embodiments, the sensor module 102 may be located
on the user's natural limb that is attached to, or associated with,
the prosthetic/orthotic device. In such an embodiment, the sensor
module is used to capture information relating to the movement of
the user's natural limb to appropriately adjust the
prosthetic/orthotic device. For example, the control system 100 may
detect the gait of the user and adjust the prosthetic/orthotic
device accordingly while the prosthetic/orthotic device is in a
swing stage of the first step. In other embodiments of the
invention, there may be a latency period in which the control
system 100 requires one or two strides before being able to
accurately determine the gait of the user and to adjust the
prosthetic/orthotic device appropriately.
[0038] Furthermore, the sensor module 102 may be used to capture
information relating to, for example, one or more of the following:
the position of the prosthetic/orthotic device with respect to the
ground; the inclination angle of the prosthetic/orthotic device;
the direction of gravity with respect to the position of the
prosthetic/orthotic device; information that relates to a stride of
the user, such as when the prosthetic/orthotic device contacts the
ground (e.g., "heel strike" or "toe strike"), is in mid-stride or
midswing, or leaves the ground (e.g., "toe off" or "heel off"), the
distance between the prosthetic/orthotic device and the ground at
the peak of the swing stage (i.e., the maximum height during the
swing stage); the timing of the peak of the swing stage;
combinations of the same and the like.
[0039] In certain preferred embodiments, the sensor module 102
provides a time series of motion signals relating to the real-time
movement of the device associated with the limb. For instance, the
sensor module 102 may comprise one or more accelerometers that
produce a continuous and/or a discrete time series of motions
signals to be analyzed by the processor 104, which process is
described in more detail below.
[0040] As depicted in FIG. 1, in certain embodiments of the
invention, the sensor module 102 is further configured to measure
environmental or terrain variables including one or more of the
following: the characteristics of the ground surface, the angle of
the ground surface, the air temperature and wind resistance. In
certain embodiments, the measured temperature may also be used to
calibrate the gain and/or bias of other sensors.
[0041] The output signal(s) of the sensor module 102 may be
generated at any predefined rate. For instance, in certain
embodiments, the sensor module 102 generates a 100 Hz output signal
representing the gait of a user. In other embodiments, the output
signal(s) of the sensor module 102 may be greater than, or less
than, 100 Hz. In yet other embodiments, the frequency of the sensor
output(s) may vary between different portions of a user's movement
(e.g., stride). Furthermore, changes in the frequency of the sensor
module output signal may be compensated for by modifying normal
data stored in the memory and used in comparison(s) with the
received sensor module signal.
[0042] The processor 104 advantageously processes data received
from other components and/or modules of the control system 100. In
certain embodiments, the processor 104 receives information from
the sensor module 102 relating to movement (e.g., gait) of the
user. In turn, the processor 104 may use such movement data to
determine one or more characteristics of the limb-motion of the
user and/or to send commands to the control drive module 110. For
example, the data captured by the sensor module 102 may be used to
generate a waveform comprising a time series of data points that
portray information relating to the gait or movement of a limb of
the user. Subsequent changes to the waveform may be identified by
the processor 104 to predict future movement of the user and to
adjust the prosthetic/orthotic device accordingly.
[0043] In certain embodiments, the processor 104 may perform signal
processing to detect one or more motion-related events. For
instance, signals relating to the sensing of movement of a
prosthetic/orthotic foot may be used to detect one or more gait
stride events, which may include, for example, heel strike, toe
down, heel off, initial push off, toe off, start of a forward
swing, mid forward swing, end of forward swing and/or heel strike
preparation.
[0044] In certain embodiments, the processor 104 may perform signal
processing to detect one or more motion-related phases or
categories. For example, detected gait events and/or the received
time series of motion signals may be analyzed in real time to
determine a motion-related phase or category. In certain
embodiments, signals relating to the sensing of movement of a
prosthetic/orthotic foot may be used to detect one or more
locomotion phases which may include, for example, walking on level
ground, walking up stairs and/or down stairs, and/or walking up an
incline and/or down a decline. In other embodiments, additional
phases or categories may be detected, such as one or more of the
following: lying down, cycling, climbing a ladder, running or the
like.
[0045] In other embodiments, the processor 104 may perform a
variety of other processing functions. For example, the processor
104 may use information received from the sensor module 102 to
detect stumbling by the user. The processor 104 may function as a
manager of communication between the components of the control
system 100. For example, the processor 104 may act as the master
device for a communication bus between multiple components of the
control system 100 and/or provide power distribution and/or
conversion to the other components of the control system 100.
[0046] In addition, the processor 104 may function so as to
temporarily suspend or decrease power to the control system 100
when a user is in a sitting or a standing position. Such control
provides for energy conservation during periods of decreased use.
The processor 104 may also process error handling, such as when
communication fails between components, an unrecognized signal or
waveform is received from the sensor module 102, or when feedback
from the control drive module 110 or the prosthetic/orthotic device
causes an error or appears corrupt.
[0047] In certain embodiments, the processor 104 generates a
security factor when analyzing information received from the sensor
module 102 and/or when sending commands to the control drive module
110. For example, the security factor may include one of a range of
values that reflects a degree of certainty of a determination made
by the processor 104. For instance, a high security value may
indicate a higher degree of certainty associated with a determined
motion-related event or phase, and a low security factor may
indicate a lower degree of certainty as to the determined event or
phase. In certain embodiments, subsequent adjustments of the
prosthetic/orthotic device are not made unless the event and/or
phase of the user is recognized with a security factor above a
predetermined threshold value.
[0048] The processor 104 may include modules that comprise logic
embodied in hardware or firmware, or that comprise a collection of
software instructions written in a programming language, such as,
for example C++. A software module may be compiled and linked into
an executable program, installed in a dynamic link library, or may
be written in an interpretive language such as BASIC. It will be
appreciated that software modules may be callable from other
modules or from themselves, and/or may be invoked in response to
detected events or interrupts. Software instructions may be
embedded in firmware, such as an EPROM or EEPROM. It will be
further appreciated that hardware modules may be comprised of
connected logic units, such as gates and flip-flops, and/or may be
comprised of programmable units, such as programmable gate arrays
or processors.
[0049] With continued reference to FIG. 1, the processor 104
further includes a memory 106 for storing instructions and/or data.
In certain embodiments, the memory 106 preferably is configured to
store data representing gait patterns or curves. For example, the
memory 106 may include experimental data representing gait curves
generated from a plurality of data sets relating to a plurality of
individuals, which experimental data is stored for comparison in
motion-related event and/or phase detection. Experimental data may
be gathered in a laboratory setting and/or in association with the
particular control system 100. In further embodiments, such data
may also be used for initial calibration of the control system
100.
[0050] In yet other embodiments, the memory 106 may further store
one or more of the following types of data or instructions: an
error log for the other components of the control system 100;
information regarding past activity of the user (e.g., number of
steps); control parameters and set points; information regarding
software debugging or upgrading; preprogrammed algorithms for basic
movements of the prosthetic or orthotic system; calibration values
and parameters relating to the sensor module 102 or other
components; instructions downloaded from an external device;
combinations of the same or the like.
[0051] The memory 106 may comprise any buffer, computing device, or
system capable of storing computer instructions and/or data for
access by another computing device or a computer processor. In
certain embodiment, the memory 106 is a cache memory. In other
embodiments of the invention, the memory 106 comprises random
access memory (RAM) or may comprise other integrated and accessible
memory devices, such as, for example, read-only memory (ROM),
programmable ROM (PROM), and electrically erasable programmable ROM
(EEPROM). In yet other embodiments, at least a portion of the
memory 106 may be separate from the processor 104. For instance,
the memory 106 may comprise a removable memory, such as a memory
card, a removable drive, or the like.
[0052] As illustrated, the processor 104 also communicates with the
interface 108, such as, for example, to receive user- or
activity-specific instructions from a user or from an external
device. For instance, the processor 104 may communicate with a
personal computer, a personal digital assistant, a cell phone, a
portable computing device, or the like, to download or receive
operating instructions. In certain embodiments, the interface 108
may comprise a network interface or a Universal Serial Bus (USB)
connector.
[0053] The control drive module 110 translates high-level plans or
instructions received from the processor 104 into low-level control
signals to be sent to the actuator 112. In certain embodiments, the
control drive module 110 comprises a printed circuit board that
implements control algorithms and tasks related to the management
of the actuator 112. The control drive module 110 may also be used
to provide feedback to the processor 104 regarding the position or
movement of the actuator 112 or prosthetic/orthotic device.
[0054] The actuator 112 provides for the controlled movement of the
prosthetic/orthotic device. For instance, the actuator 112 may
advantageously control movement of the prosthetic/orthotic device
to execute angular and/or rotational displacements synchronized
with the user's movement or locomotion. For example, the actuator
112 may be similar to one of the actuators described in copending
U.S. application Ser. No. 11/056,344, filed Feb. 11, 2005.
[0055] The power module 114 includes one or more sources and/or
connectors usable to power the control system 100. In one
embodiment, the power module 114 is advantageously portable, and
may include, for example, a rechargeable battery. As illustrated,
the power module 114 communicates with the control drive module 110
and the processor 104. In other embodiments, the power module 114
communicates with other control system 100 components instead of,
or in combination with, the control drive module 110 and the
processor 104. For example, in one embodiment, the power module 114
communicates directly with the sensor module 102. Furthermore, the
power module 114 may communicate with the interface 108 such that a
user is capable of directly controlling the power supplied to one
or more components of the control system 100.
[0056] While the control system 100 has been described with
reference to certain embodiments, other variations of the control
system 100 may be used. For example, the control system 100 may
operate without the interface 108. Furthermore, in certain
embodiments, the control system 100 is based on a distributed
processing system wherein the different functions performed by the
pro sthetic/orthotic system, such as sensing, data processing, and
actuation, are performed or controlled by multiple processors that
communicate with each other. In yet other embodiments, the
processed data may be used to trigger an action other than
movement, such as, for example, the illumination of a diode or the
emitting of an alarm or an audible alert.
[0057] It is also contemplated that the components of the control
system 100 may be integrated in different forms. For example, the
components can be separated into several subcomponents or can be
separated into more devices that reside at different locations and
that communicate with each other, such as through a wired or
wireless network. For example, in one embodiment, the modules may
communicate through RS232 or serial peripheral interface (SPI)
channels. Multiple components may also be combined into a single
component.
[0058] With continued reference to the control system 100 of FIG.
1, in certain embodiments of the invention, the sensor module 102
provides data relating to the linear acceleration and/or angular
acceleration of a prosthetic/orthotic device, and such data is used
to determine one or more motion-related events and phases and/or to
appropriately adjust the prosthetic/orthotic device. For instance,
one or more sensors of the sensor module 102 may measure
acceleration of the prosthetic/orthotic device in three
substantially, mutually perpendicular axes. For example, three
accelerometers may be used to measure acceleration in the three
orthogonal axes to sense motion of the prosthetic/orthotic device
and to generate an associated time series of motion signals.
[0059] Various aspects of the received time series signal(s) may be
used by the processor 104. For example, in certain embodiments, the
processor uses the signal itself, a first derivative (e.g., slope)
and/or a second derivative (e.g., slope rate) thereof to determine
a motion-related event and/or phase.
[0060] With reference to a prosthetic/orthotic foot device, linear
acceleration detection may include sensing downward acceleration
(e.g., along an x-axis), forward acceleration (e.g., along a
y-axis) and inward acceleration (e.g., along a z-axis) from the
perspective of the left foot of the user. For instance, detection
of linear acceleration may be performed according to the following
three equations:
.differential. 2 x .differential. t : downward acceleration
.differential. 2 y .differential. t : forward acceleration
.differential. 2 z .differential. t : inward acceleration
##EQU00001##
[0061] In certain embodiments, both the downward acceleration and
the forward acceleration measurements are used by the processor 104
to estimate a motion-related event and/or phase of a user. In
certain embodiments, the inward acceleration measurement is used by
the processor 104 for quality control to determine if the sensing
module 102 is properly calibrated and/or positioned or is working
correctly.
[0062] Furthermore, the sensing module 102 may also detect angular
acceleration, such as angular acceleration in three substantially
orthogonal planes. For instance, with reference to a
prosthetic/orthotic foot device, angular acceleration may include
sensing, with one or more accelerometers (e.g., one or more
gyroscopes), in a transverse (x-y) plane, in a coronal plane (y-z)
and in a sagittal plane (e-x) of a user. In certain embodiments,
detection of angular acceleration is performed according to the
following three equations:
.differential. 2 .theta. x .differential. t : angular acceleration
in transverse plane .differential. 2 .theta. y .differential. t :
angular acceleration in coronal plane .differential. 2 z
.differential. t : angular acceleration in sagittal plane
##EQU00002##
[0063] In certain embodiments, either or both of the angular
accelerations in the transverse and coronal planes are used to
estimate a quality of detection by the sensing module 102. The
angular acceleration in the sagittal plane may be used to estimate
motion-related events and/or phases of the user.
[0064] In certain embodiments, one or more acceleration sensors may
include an XSENS acceleration sensor, such as the MT9 Inertial 3D
motion tracker commercially available from XSENS Motion
technologies (Netherlands). In yet other embodiments, other
suitable types of acceleration or movement reading sensors may also
be used. For example, the sensor module 102 may include a gyroscope
configured to measure angular speed. In other embodiments, the
sensor module 102 includes a plantar pressure sensor configured to
measure, for example, the vertical plantar pressure of a specific
underfoot area. Other movement signal(s) in a given reference plane
can also be utilized, such as, for example, measurements of
centrifugal force, magnetic field and/or electromagnetic field.
[0065] In yet other embodiments, the sensor module 102 may include
one or more of the following in place of, or in combination with,
at least one accelerometer: kinematic sensors, multi- and/or
single-axis gyroscopes, multi-axis accelerometers, load sensors,
flex sensors or myoelectric sensors that may be configured to
capture data from the user's natural limb. U.S. Pat. No. 5,955,667,
U.S. Pat. No. 6,301,964, and U.S. Pat. No. 6,513,381, also
illustrate examples of sensors that may be used with embodiments of
the invention, which patents are herein incorporated by reference
in their entireties.
[0066] Furthermore, in certain embodiments of the invention, the
sensor module 102 may be configured to monitor motion of a limb (or
a device associated with a limb) with respect to a global reference
instead of, or in combination with, the local tracking of movement.
For example, the sensor module 102 may include a sensor that
detects movement with respect to another reference plane or object,
such as the earth, as is done in global positioning systems
(GPS).
[0067] FIGS. 2A and 2B illustrate exemplary data detection sets
relating to level ground walking by a user and include, for
example, signals indicative of the motion of a prosthetic foot. As
shown, the six graphs illustrate relative measurements of linear
acceleration (i.e., downward, forward and inward directions) and
angular acceleration (i.e., transverse, coronal and sagittal
planes). In certain embodiments of the invention, such data sets
are generated by the sensor module 102 and are further analyzed by
the processor 104 to determine characteristics of the gait of the
user. In other embodiments of the invention, other received signals
may relate to motion of another type of prosthetic limb (e.g., an
arm) or relate to the motion of orthotic devices.
[0068] In certain embodiments of the invention, the processor 104
advantageously performs a time series analysis on the sensed motion
signals, or data points relating thereto, to determine
characteristics of a gait of a user. Such a time series analysis
includes processing the sequence(s) of received measurements (e.g.,
acceleration measurements) with the general assumptions that the
measurements follow non-random orders and that successive values in
the received sensor data represent consecutive measurements taken
at equally spaced time intervals.
[0069] For example, in certain preferred embodiments, one or more
data points of the received time series of motion signals is
associated with one or more timestamps that identify portions of
the signal for normalization and/or for comparison with stored data
signals. The timestamps allow for different signals having similar
timestamps to be compared and processed by the processor 104. For
instance, the one or more timestamps associated with the received
sensor signal may be based on a detected or determined limb-motion
event (e.g., a heel strike or a toe-off event). That is, the
timestamp correlates the associated data point with a particular
point in time after the determined event has occurred.
[0070] The timestamps also preferably allow data sets having a
different number of values (e.g., a different rate) to be compared
by the processor 104. For example, a received time series of motion
signals may have a data set of eighty points for a particular
duration of time, while a stored data set may include one hundred
points for the same duration. By correlating the timestamps between
the two data sets, the processor 104 is able to appropriately
expand and/or shift the received data set, such as by
interpolation, to have the same number of data points as, and to
line up in time with, the stored data set.
[0071] FIG. 3 illustrates an exemplary flowchart of a gait stride
detection process 300. In certain embodiments, the gait detection
process 300 is performed at least in part by the control system 100
of FIG. 1 to determine a motion-related event and/or phase of a
user and to appropriately adjust an actuating mechanism of a
corresponding prosthetic/orthotic device. For exemplary purposes,
the gait detection process 300 will be described with reference to
the components of the control system 100 in the context of a
motion-controlled prosthetic foot. A skilled artisan, however, will
recognize from the disclosure herein a wide variety of other
hardware and/or software systems or devices capable of performing
at least a portion of the gait detection process 300.
[0072] The gait detection process 300 begins with block 305,
wherein the processor 104 receives measurement data from the sensor
module 102. In certain embodiments, the measurement data comprises
linear acceleration data and/or angular acceleration data sensed
with respect to the movement of the prosthetic ankle device. For
instance, measurement data may include at least the following six
subsets of data received from at least one accelerometer positioned
on the prosthetic ankle device: linear acceleration data in the
downward, forward and inward directions; and angular acceleration
data in the transverse, coronal and sagittal planes. In other
embodiments, the measurement data may relate to the movement of a
healthy limb and be used to control the movement of a corresponding
artificial limb.
[0073] In certain embodiments, the measurement data is preferably
received as a time series of data points, wherein the measurement
data includes a sequence of data points ordered in the time in
which they were observed. In certain embodiments, the time series
of data points is a discrete time series set wherein acceleration
measurements of the prosthetic device are taken every 10
milliseconds. In yet other embodiments, other frequencies of
measurements may be used and/or the frequency of measurements may
be variable over a particular period of time and/or during
particular portions of the user's gait. In yet other embodiments,
the received data may be in the form of a continuous time series
with either a uniform or non-uniform sampling rate.
[0074] After receiving the measurement data, the processor 104
preferably filters the data (block 310) in order to predict future
data points and/or to provide a smoother signal for the subsequent
detection routines. In certain embodiments, such filtering may
include predictive, static and/or adaptive filtering. For instance,
an autoregressive (AR) filter, such as for example, a Kalman
filter, may process the last "n" data points in the received motion
signal to remove random error. In such embodiments, the filter may
determine how much weight is to be given to each of a number of
past data points in performing the current data analysis. This
advantageously provides for a smoother signal by filtering out
fluctuation in the signal (e.g., noise) and signal abnormalities.
For instance, the filter may determine that, during the processing
of a current data input, forty percent of the value associated with
the previous (last) data point is to be used, thirty percent of the
value associated with the second-to-last data point is to be used,
fifteen percent of the value associated with the third-to-last data
point is to be used, and so forth.
[0075] In other embodiments, the received measurement data may be
processed by other regressive techniques (e.g., linear, k'th order
polynomial, quadratic, exponential, harmonic) and/or other filters
(e.g., moving average (MA), autoregressive moving average (ARMA),
autoregressive integrated moving average (ARIMA), low pass, high
pass, fuzzy, combinations of the same and the like) for producing a
smoother signal.
[0076] For example, in certain embodiments, an autoregressive
filter is used to calculate the slope of a received time series of
motion signals related to linear acceleration and/or a rate of turn
(slope rate) of a received time series of motion signals related to
angular acceleration. This calculated data may then be used to
determine a current motion-related event. For instance, in certain
embodiments, the processor 104 uses the following equations to
calculate the slope and slope rate for at least one time series of
motion signals:
AR := [ ar 0 ar 1 ar i ar n ] ##EQU00003## i = 0 n ar i = 1
##EQU00003.2## ar i .di-elect cons. [ 0 , 1 ] , i = 0 , , n
##EQU00003.3## .differential. .differential. t ( .differential. 2 X
l , j .differential. t 2 ) = k = j - n j 1 .DELTA. t (
.differential. 2 X l , k .differential. t 2 - .differential. 2 X l
, k - 1 .differential. t 2 ) AR j - k j .gtoreq. n + 1
##EQU00003.4## .differential. 2 .differential. t 2 ( .differential.
2 X l , j .differential. t 2 ) = k = j - n n 1 .DELTA. t 2 (
.differential. 2 X l , k .differential. t 2 - 2 .differential. 2 X
l , k - 1 .differential. t 2 + .differential. 2 X l , k - 2
.differential. t 2 ) .DELTA. t 2 AR j - k j .gtoreq. n + 2
##EQU00003.5## .differential. 2 X l , j .differential. t 2 := [
.differential. x 1 2 .differential. t 2 .differential. y 1 2
.differential. t 2 .differential. z 1 2 .differential. t 2
.differential. .theta. x , 1 2 .differential. t 2 .differential.
.theta. y , 1 2 .differential. t 2 .differential. .theta. z , 1 2
.differential. t 2 .differential. x 2 2 .differential. t 2
.differential. y 2 2 .differential. t 2 .differential. z 2 2
.differential. t 2 .differential. .theta. x , 2 2 .differential. t
2 .differential. .theta. y , 2 2 .differential. t 2 .differential.
.theta. z , 2 2 .differential. t 2 .differential. x 3 2
.differential. t 2 .differential. y 3 2 .differential. t 2
.differential. z 3 2 .differential. t 2 .differential. .theta. x ,
3 2 .differential. t 2 .differential. .theta. y , 3 2
.differential. t 2 .differential. .theta. z , 3 2 .differential. t
2 .differential. x m 2 .differential. t 2 .differential. y m 2
.differential. t 2 .differential. z m 2 .differential. t 2
.differential. .theta. x , m 2 .differential. t 2 .differential.
.theta. y , m 2 .differential. t 2 .differential. .theta. z , m 2
.differential. t 2 ] j = 1 N ##EQU00003.6##
wherein n is a number of data points; AR is a vector holding n data
point values that determine how much weight is given to past data
values so as to filter the signal prior to further processing; X is
a position matrix of the monitored object; j is a relative position
in time of a particular data point; t is time; and .DELTA.t is a
time between data points (e.g., ten milliseconds). The bottom
equation shown above comprises a signal matrix that may be used to
process a variety of forms of data (e.g., acceleration and/or
gyroscope data) representing an activity measurement signal.
[0077] In yet other embodiments, different filtering techniques may
be used with different data sets and/or during different detected
motion-related events. For example, linear acceleration signals may
undergo a different filter process than angular acceleration
signals received during the same time period.
[0078] In yet other embodiments, each motion-related event is
associated with its own stored data set. Each data set may, in
turn, include a plurality of parameters for comparison with the
received time series of motion signals. For instance, each data set
relating to event recognition may include between three or more
parameters, such as, for example, between three and twelve
parameters. Generally, the more parameters that are used in the
data comparison, the more accurate is the event and/or phase
detection.
[0079] For instance, the parameters may include values and their
first and second derivatives received from between two and six
motion sensors. For example, in an embodiment, one of the
parameters may include a slope of the downward acceleration when
threshold values of a gyroscope signal have been met in the
sagittal plane. Such may further trigger the processing of forward
acceleration data and the rate of turn of the forward
acceleration.
[0080] Such parameters may also be used in determining a security
value for the event and/or phase determination. If several or all
of the parameters are met in a comparison between a stored data set
and a received time series of motion signals, the processor 104 may
generate a high security value indicating a high likelihood that an
accurate determination of the event and/or phase has been made.
Likewise, if two parameters are used and/or set in such a
comparison, the processor 104 may generate a low security
value.
[0081] After the data has been received and/or filtered, the
processor 104 determines a motion-related event based on the
received data (block 315). For instance, processor 104 may detect
an ankle-motion related event of the corresponding prosthetic ankle
device, such as, for example, heel strike, toe down, heel off, toe
off, mid-swing or end of swing.
[0082] If the event detected by the processor 104 is related to a
swing stage (block 320), the gait detection process moves to block
325. The processor 104 then determines if the user is walking on
level ground. If the processor 104 determines that the user in
walking on level ground, the gait detection process 300 proceeds
with block 330. At block 330, the processor 104 determines if there
has been a toe-off event (e.g., the "toe" of the prosthetic foot
leaving the ground during a stride). If there has been a toe-off
event detected, the processor 104 determines if a security
threshold has been met (block 335). For example, in determining the
toe-off event, the processor 104 may also generate a security
value, as discussed previously, that represents the probability or
percent certainty that the toe-off event has been correctly
detected.
[0083] If the security value is not above a particular threshold
(e.g., low likelihood of correctness of determination), or if the
processor 104 does not detect a toe-off event at block 330, the
gait detection process 300 moves to block 340, and no action is
taken on the actuator 112. For instance, an actuator of the
prosthetic ankle device may be kept in its current state or
position, or the actuator may automatically return to a default
state or position.
[0084] If the security value does meet the predetermined threshold
in block 335, the gait detection process 300 moves to block 345. At
block 345, the processor 104 outputs commands for appropriately
adjusting the actuator 112. For example, the processor 104 may
output a signal to the control drive module 110 to cause the
prosthetic ankle device to dorsiflex such that the toe of the
device is raised after toe-off.
[0085] With reference to block 325, if the user is not walking on
level ground, or if the event detected by the processor 104 at
block 320 is not related to a swing stage, the gait detection
process 300 proceeds with block 350. At block 350, the processor
104 compares the received time series data with stored measurement
data. For instance, the memory 106 may store normal data for a
plurality of different motion-related phases, which normal data is
then compared with a normalized version of the received data in
order to determine the current phase. In certain embodiments, the
memory 106 includes normal data relating to level ground walking,
incline and decline walking, and walking up and down stairs.
Furthermore, the normal data may be based on information that is
general to all users, or the normal data may be determined from
previous strides of the particular user.
[0086] In certain embodiments, the received time series of motion
signals is normalized by the processor 104 according to the
following equations:
DataNorm = [ .differential. 2 x 1 ' .differential. t 2
.differential. 2 y 1 ' .differential. t 2 .differential. 2 z 1 '
.differential. t 2 .differential. 2 .theta. x , 1 ' .differential.
t 2 .differential. 2 .theta. y , 1 ' .differential. t 2
.differential. 2 .theta. z , 1 ' .differential. t 2 S 1 '
.differential. 2 x N ' .differential. t 2 .differential. 2 y N '
.differential. t 2 .differential. 2 z N ' .differential. t 2
.differential. 2 .theta. x , N ' .differential. t 2 .differential.
2 .theta. y , N ' .differential. t 2 .differential. 2 .theta. z , N
' .differential. t 2 S N ' ] ##EQU00004## dt = L - k n - 1 , t i '
= t i - 1 ' + dt , t = t i ' , .xi. = t - t i ' ##EQU00004.2##
.differential. 2 x i ' .differential. t 2 = .differential. 2 x t
.omega. - 1 .differential. t 2 .xi. + .differential. 2 x t .omega.
.differential. t 2 ( 1 - .xi. ) , .differential. 2 .theta. x , i '
.differential. t 2 = .differential. 2 .theta. x , t .omega. - 1
.differential. t 2 .xi. + .differential. 2 .theta. x , t .omega.
.differential. t 2 ( 1 - .xi. ) , .differential. 2 y i '
.differential. t 2 = .differential. 2 y t .omega. - 1
.differential. t 2 .xi. + .differential. 2 y t .omega.
.differential. t 2 ( 1 - .xi. ) , .differential. 2 .theta. y , i '
.differential. t 2 = .differential. 2 .theta. y , t .omega. - 1
.differential. t 2 .xi. + .differential. 2 .theta. y , t .omega.
.differential. t 2 ( 1 - .xi. ) , .differential. 2 z i '
.differential. t 2 = .differential. 2 z t .omega. - 1
.differential. t 2 .xi. + .differential. 2 z t .omega.
.differential. t 2 ( 1 - .xi. ) , .differential. 2 .theta. y , i '
.differential. t 2 = .differential. 2 .theta. y , t .omega. - 1
.differential. t 2 .xi. + .differential. 2 .theta. y , t .omega.
.differential. t 2 ( 1 - .xi. ) , , i = 0 N ##EQU00004.3## S i ' =
S t .omega. ##EQU00004.4##
wherein .differential.t is a difference in time between data
points; L is an end stream point identifier (e.g., end of stride);
k is a start stream point identifier (e.g., beginning of stride); n
is a number of points in a corresponding comparison data matrix;
t'_i is a new timestamp in a normalized data matrix; and .xi. is a
distance from the new timestamp to time points of the normalized
dataset. Moreover, the top equation illustrated above represents an
information matrix for raw data received from sensors, such as from
the sensor module 102.
[0087] Once the received data has been normalized, the processor
104 is able to compare the normalized data with the stored normal
data (e.g., in the comparison matrix) for different phases in order
to determine the current motion-related phase of the user (block
355). For instance, the processor 104 may determine from the
comparison the type of surface on which the user is walking (e.g.,
ramp, stairs, level ground) and/or the slope of the surface.
[0088] After the current phase is determined, the gait detection
process 300 proceeds with block 360, wherein the processor 104
stores in the memory 106 the received data, the determined event,
the determined phase, a security value and/or timestamps associated
with the received time series signal. For example, in certain
embodiments, the processor 104 may store data from multiple
strides, such as the previous three strides of the user. This
information stored in the memory 106 may then be preferably used in
future data processing, such as during the comparison routine at
block 350.
[0089] The gait detection process 300 then moves to block 335 to
determine if a security threshold has been met for the determined
phase. If the generated security value is not above the
predetermined threshold, the gait detection process 300 moves to
block 340, and no action is taken on the actuator 112. If the
security value does meet the predetermined threshold in block 335,
the gait detection process 300 moves to block 345. At block 345,
the processor 104 outputs commands for appropriately adjusting the
actuator 112 based on the determined phase.
[0090] FIG. 4 illustrates a flowchart of an exemplary event
detection process 400 according to certain embodiments of the
invention. For instance, the event detection process 400 may be at
least partially performed during blocks 315-345 of the gait stride
detection process 300 of FIG. 3. For exemplary purposes, the event
detection process 400 will be described with reference to the
components of the control system 100 in the context of a
motion-controlled prosthetic foot. In particular, the event
detection process 400 will be described with reference to detecting
a toe-off event of the motion-controlled prosthetic foot. A skilled
artisan, however, will recognize from the disclosure herein a wide
variety of other hardware and/or software systems or devices
capable of performing at least a portion of the event detection
process 400.
[0091] The event detection process 400 begins at block 405 by
determining if the prosthetic foot device is in a stance stage.
That is, the processor 104 determines from received measurement
data if at least a portion of the prosthetic foot device is in
contact with the ground. If the prosthetic foot device is not in a
stance stage, the event detection process 400 moves to block 410 to
perform swing stage event detection. If the prosthetic foot device
is in a stance stage, the event detection process 400 proceeds with
block 415. At block 415, the processor 415 performs a time series
analysis on the received measurement data, such as is discussed
above. For instance, the processor 104 may use a Kalman filter to
process the received time series of motion signals.
[0092] At block 420, the processor 104 determines if a toe-off
event has taken place. If a toe-off event has not occurred, the
event detection process 400 returns to block 415 wherein the
processor 104 continues to analyze received data. If a toe-off
event has occurred, the processor 104 stores the toe-off values in
the memory 106 (block 425).
[0093] At block 430, the processor 104 then determines if the user
is walking on level ground, such as by, for example, analyzing the
received measurement data. If the user is walking on level ground,
the processor 104 then determines if the security threshold has
been met (block 435). For instance, in certain embodiments, the
processor 104 produces at least one security value when determining
a motion-related event and/or phase. Such a security value may
represent the probability or percent certainty that the particular
event or phase has been correctly detected.
[0094] If the generated security value does not meet or exceed the
predetermined threshold, or if at block 430 the processor 104 does
not determine that the user is walking on level ground, the event
detection process 400 moves to block 440, and no action is taken on
the actuator 112. If, however, the security threshold is met, the
processor 104 outputs commands for appropriately adjusting the
actuator 112 (block 445). For example, the processor 104 may output
a signal to the control drive module 110 to cause the prosthetic
ankle device to dorsiflex such that the toe of the device is raised
after toe off.
[0095] FIGS. 5A and 5B illustrate a dataflow diagram of data
comparison process 500 according to certain embodiments of the
invention. For example, the comparison process 500 may be performed
at least in part during several of the blocks (e.g., blocks 315,
320, 330 and 350) of the gait stride detection process 300 of FIG.
3. For exemplary purposes, the data comparison process 500 will be
discussed with reference to detecting and processing gait events
relating to a motion-controlled prosthetic foot. A skilled artisan,
however, will recognize from the disclosure herein a wide variety
of other hardware and/or software systems or devices capable of
performing at least a portion of the comparison process 500.
[0096] The illustrated comparison process 500 includes a data
stream input 502 that includes information relating to movement of
the motion-controlled prosthetic foot. In certain embodiments, the
data stream input comprises at least one time series of data
signals indicative of acceleration (e.g., linear acceleration
and/or angular acceleration) of the prosthetic foot.
[0097] As shown, the comparison process 500 includes several
different routines, each of which relates to a motion-related event
of the prosthetic foot. In particular, the comparison process 500
includes a heel-strike routine 504, a toe-on-ground routine 506, a
heel-off-ground routine 508, a toe off routine 510, a midswing
routine 512 and a second heel-strike routine 514. As is also
illustrated, the time from the heel-strike event to the toe-off
event is labeled as a stance stage, and the time from the toe-off
event to the heel-strike event is labeled as a swing stage.
[0098] In certain embodiments, the data stream input 502 is
received by all the routines at substantially the same time for
further processing and event detection. In general, the data flow
of the comparison process 500 occurs from left to right, as
illustrated by the block arrows in FIGS. 5A and 5B. For example,
during normal level ground walking, the processing and detection of
a heel-strike event will occur prior to the processing and
detection of a toe-on-ground event. In certain embodiments, the
detection routine of one particular event is not triggered or
initiated unless the previous gait event has been detected.
[0099] As shown in FIGS. 5A and 5B, the comparison process 500
utilizes a "HEEL" variable and a "TOE" variable to process the data
stream input information 502. In particular, the HEEL variable is
assigned a value of "1" when the processor 104 determines that the
heel portion of the prosthetic foot device is in contact with the
ground. The HEEL variable is assigned a value of "0" when the
processor 104 determines that the heel of the prosthetic foot
device is not in contact with the ground (e.g., is in a swing
stage). Likewise, the TOE variable is assigned a value of "1" when
the processor 104 determines that the toe portion of the prosthetic
foot device is in contact with the ground. The TOE variable is
assigned a value of "0" when the processor 104 determines that the
toe of the prosthetic foot device is not in contact with the ground
(e.g., is in a swing stage).
[0100] In certain embodiments, the values of the HEEL and/or TOE
variables are derived from acceleration measurements received by
the processor. In yet other embodiments, pressure sensors placed
near the toe and the heel portions of the prosthetic foot device
are used to set the values for the TOE and HEEL variables.
[0101] As illustrated, the heel-strike routine 504 begins at block
520 by determining if the HEEL variable has changed from a "0"
value to a "1" value, indicating contact of the heel with a ground
surface. If the HEEL variable remains a "0" value, the heel-strike
routine 504 continues with block 520.
[0102] If the heel-strike routine 504 does detect a transition in
the value of the HEEL variable from "0" to "1," the processor 104
then stores a timestamp of this change in the memory 106 (block
522). Furthermore, the processor 104 compares (at block 524) the
received data stream input data with stored normal data (block
526). As shown, the normal data comprises data that relates to a
heel-strike event, wherein there is a transition from a midswing
stage (e.g., both HEEL and TOE are equal to "0") to a stage wherein
HEEL equals "1" and TOE equals "0." For instance, the normal data
may comprise previously recorded and processed data for the
particular prosthetic foot. In other embodiments, the normal data
may be generalized data applicable to a wide variety of users.
[0103] In certain embodiments, each of the distinct gait events is
advantageously associated with its own normal data. This is
especially useful in situations wherein the quality of data differs
between the gait events. For example, it may be easier to
accurately determine when a heel-strike event occurs than when a
midswing event occurs, and the quality of data may be different for
each event.
[0104] Once the received data has been compared with the stored
data, the processor 104 determines if a true heel-strike event has
occurred, and the processor 104 stores the new generated data, such
as in the memory 106 (block 528). This stored data can then be used
in later comparisons of the heel-strike routine 504.
[0105] Once a heel-strike event has been detected, the comparison
process 500 proceeds with the toe-on-ground routine 506. The
toe-on-ground routine 506 begins at block 530 by determining if the
TOE variable has changed from a "0" value to a "1" value,
indicating contact of the toe portion with a ground surface. If the
TOE variable remains a "0" value, the toe-on-ground routine 506
continues with block 530.
[0106] If the toe-on-ground routine 506 does detect a transition in
the value of the TOE variable from "0" to "1," the processor 104
then stores a timestamp of this change in the memory 106 (block
532). Furthermore, the processor 104 compares (at block 534) the
received data stream input data with stored normal data (block
536). As shown, the normal data comprises data that relates to a
toe-on-ground event, wherein there is a transition in the value of
the TOE variable from "0" to "1" and wherein the HEEL variable
remains equal to Once the received data has been compared with the
stored data, the processor 104 determines if a true toe-on-ground
event has occurred, and the processor 104 stores the new generated
data, such as in the memory 106 (block 538). This stored data can
then be used in later comparisons of the toe-on-ground routine
506.
[0107] Once a toe-on-ground event has been detected, the comparison
process 500 proceeds with the heel-off-ground routine 508. The
heel-off-ground routine 508 begins at block 540 by determining if
the HEEL variable has changed from a "1" value to a "0" value,
indicating a separation between the heel portion of the prosthetic
device and a ground surface. If the HEEL variable remains a "1"
value, the heel-off-ground routine 508 continues with block
540.
[0108] If the heel-off-ground routine 508 does detect a transition
in the value of the HEEL variable from "1" to "0," the processor
104 then stores a timestamp of this change in the memory 106 (block
542). Furthermore, the processor 104 compares (at block 544) the
received data stream input data with stored normal data (block
546). As shown, the normal data comprises data that relates to a
heel-off-ground event, wherein there is a transition in the value
of the HEEL variable from "1" to "0" and wherein the TOE variable
remains equal to Once the received data has been compared with the
stored data, the processor 104 determines if a true heel-off-ground
event has occurred, and the processor 104 stores the new generated
data, such as in the memory 106 (block 548). This stored data can
then be used in later comparisons of the heel-off-ground routine
508.
[0109] Once a heel-off-ground event has been detected, the
comparison process 500 proceeds with the toe-off-ground routine
510. The toe-off-ground routine 510 begins at block 550 by
determining if the TOE variable has changed from a "1" value to a
"0" value, indicating a separation between the toe portion of the
prosthetic device and a ground surface. If the TOE variable remains
a "1" value, the toe-off-ground routine 510 continues with block
550.
[0110] If the toe-off-ground routine 510 does detect a transition
in the value of the TOE variable from "1" to "0," the processor 104
then stores a timestamp of this change in the memory 106 (block
552). Furthermore, the processor 104 compares (at block 554) the
received data stream input data with stored normal data (block
556). As shown, the normal data comprises data that relates to a
toe-off-ground event wherein there is a transition in the value of
the TOE variable from "1" to "0" and wherein the HEEL variable
remains equal to Once the received data has been compared with the
stored data, the processor 104 determines if a true toe-off-ground
event has occurred, and the processor 104 stores the new generated
data, such as in the memory 106 (block 558). This stored data can
then be used in later comparisons of the toe-off-ground routine
510.
[0111] Once a toe-off-ground event has been detected, the
comparison process 500 proceeds with the midswing routine 512. The
midswing routine 510 begins at block 550 by determining if a
midswing state has been attained. For example, in certain
embodiments, the processor 104 may analyze how much time has passed
since the detection of the toe-off-ground event (e.g., how long the
prosthetic foot has not been contacting the ground) to determine
what point the user reach in his or her swing. For instance, if the
swing stage of a user's stride has averaged approximately one
second, the processor may determine the midswing state to be
approximately 0.5 second after the detection of the toe-off-ground
event.
[0112] In other embodiments, the processor 104 may analyze
acceleration measurements to detect a midswing state. For instance,
the processor 104 may process linear acceleration measurements in
the downward and/or forward directions to determine when the
prosthetic foot has reached the peak position of the swing and has
begun to move toward the ground surface. If the midswing state has
still not been reached, the midswing routine 512 continues with
block 560.
[0113] If the midswing state has been reached, the processor 104
then stores a timestamp of this point in the memory 106 (block
562). Furthermore, the processor 104 compares (at block 564) the
received data stream input data with stored normal data (block
566). As shown, the normal data comprises data that relates to a
detected midswing event, wherein TOE variable and the HEEL variable
are both equal to "0."
[0114] Once the received data has been compared with the stored
data, the processor 104 determines if a true midswing event has
occurred, and the processor 104 stores the new generated data, such
as in the memory 106 (block 568). This stored data can then be used
in later comparisons of the midswing routine 512.
[0115] Once a midswing event has been detected, the comparison
process 500 returns to a heel-strike routine, which is illustrated
in FIGS. 5A and 5B as the second heel-strike routine 514. The
second heel-strike routine 514 is generally the same as the
heel-strike routine 504. That is, the second heel-strike routine
514 begins by determining if the HEEL variable has changed from a
"0" value to a "1" value, indicating contact between the heel
portion of the prosthetic device and the ground surface. As can be
seen, the routines of the comparison process 500 may be repeated,
as appropriate, throughout the gait of the user.
[0116] FIG. 6 illustrates an exemplary embodiment of a lower-limb
prosthesis usable with embodiments of the present invention. In
particular, FIG. 6 illustrates a prosthetic ankle device 600 having
a lower limb member 602 coupled to a foot unit 604. In certain
embodiments, an actuator 606 actively controls an angle between the
lower limb member 602 and the foot unit 604 based on control
signals received from a processor, as described in more detail
previously. In certain embodiments, a frame 608 houses a sensor
module, such as the sensor module 102 of FIG. 1, which may include
one or more sensors usable to monitor motion of the prosthetic
ankle device 600. Further details of motion-controlled foot units
usable with embodiments of the invention are disclosed in U.S.
patent application Ser. No. 11/219,317, filed Sep. 1, 2005, and
entitled "ACTUATOR ASSEMBLY FOR PROSTHETIC OR ORTHOTIC JOINT," and
U.S. patent application Ser. No. 11/218,923, filed Sep. 1, 2005,
and entitled "SENSING SYSTEM AND METHOD FOR MOTION-CONTROLLED FOOT
UNIT," each of which is hereby incorporated herein by reference in
its entirety to be considered a part of this specification.
[0117] It is contemplated that the above-described systems may be
implemented in prosthetic or orthotic systems other than
transtibial, or below-the-knee, systems. For example, in one
embodiment of the invention, the prosthetic or orthotic system may
be used in a transfemoral, or above-the-knee, system, such as is
disclosed in U.S. patent application Ser. No. 11/123,870, filed May
6, 2005, and entitled "MAGNETORHEOLOGICALLY ACTUATED PROSTHETIC
KNEE;" U.S. patent application Ser. No. 11/077,177, filed Mar. 9,
2005, and entitled "CONTROL SYSTEM AND METHOD FOR A PROSTHETIC
KNEE;" U.S. Pat. No. 6,764,520, issued on Jul. 20, 2004, and
entitled "ELECTRONICALLY CONTROLLED PROSTHETIC KNEE;" and U.S. Pat.
No. 6,610,101, issued Aug. 26, 2003, and entitled "SPEED-ADAPTIVE
AND PATIENT-ADAPTIVE PROSTHETIC KNEE," each of which is hereby
incorporated herein by reference in its entirety and is to be
considered as part of this specification. For example, the
prosthetic or orthotic system may include both a prosthetic or
orthotic ankle and/or a prosthetic or orthotic knee.
[0118] Moreover, embodiments of the invention disclosed herein may
be performed by one or more software modules. For example, an
embodiment of the invention may include a machine loadable software
program for a processor for controlling the movement of a device
associated with a limb. The software program may include an input
module, a filter module, a comparison module, and a control module.
The input module may be configured to receive a time series of
motion signals. The filter module may be configured to process the
time series of motion signals and/or to generate a plurality of
filtered signals. The comparison module may be configured to
compare the plurality of filtered signals with a plurality of
sample signals and configured to generate a gait event selection
signal indicative of the movement of a device associated with a
limb. The control module may be configured to generate a control
signal based at least in part on the gait event selection signal,
wherein the control signal is capable of controlling the movement
of the device associated with a limb. Furthermore, the software
module(s) may include, for example, an AR filter and/or a Kalman
filter.
[0119] While certain embodiments of the inventions have been
described, these embodiments have been presented by way of example
only, and are not intended to limit the scope of the disclosure.
Indeed, the novel methods and systems described herein may be
embodied in a variety of other forms. For example, the foregoing
may be applied to the motion-control of joints other than the
ankle, such as a knee or a shoulder. Furthermore, various
omissions, substitutions and changes in the form of the methods and
systems described herein may be made without departing from the
spirit of the disclosure. The accompanying claims and their
equivalents are intended to cover such forms or modifications as
would fall within the scope and spirit of the disclosure.
* * * * *