Abstract:
This gait analysis apparatus comprises three, and preferably four, vertical force sensors disposed between a treadmill and the ground. When a person walks on the treadmill belt, each force sensor emits an electronic signal proportional to the load on the frame. The sensors measure the load hundreds of times per second and that data, in combination with the speed of the treadmill belt, enables a processing unit to calculate many gait parameters. The resultant calculations are displayed to the clinician in numeric and graphical formats. Due largely to the few number of force sensors, the apparatus is relatively inexpensive compared to existing gait parameter apparatuses and can be easily retrofitted to existing treadmills by either replacing the treadmill&#39;s existing ground supports with force sensors or resting the treadmill on top of a frame that has integral force sensors.

Description:
FIELD OF INVENTION 
     This invention relates generally to devices for measuring gait parameters and more particularly to an apparatus for a treadmill that measures gait parameters using four or fewer force sensors. 
     BACKGROUND 
     Clinicians working in rehabilitation settings have a need to easily quantify their patients&#39; gait parameters in order to objectively document effectiveness of therapeutic interventions. Historically, however, no equipment has been readily available for them to do so easily. Instead, gait measurement devices have historically come in three variations. One version uses external video capture with markers on the user to identify the real-time location and movement of specific locations on the user. Gait parameters can be extrapolated based upon the location and movement of these markers. This approach requires significant costs for the associated hardware and software. It also requires excessive set up and calibration time to properly place each camera in a location that captures the data appropriately. It also requires a fairly large portion of the room to be dedicated to the video capture system. The comprehensive data provided by these systems is sophisticated and detailed enough to be used for research purposes, and is more than that needed for a typical clinician. 
     A second version uses multiple force sensors embedded across the entire treadmill deck to sense the vertical force, or load, on the deck. Force sensors are expensive and an array of them is geometrically more expensive. And, although an array of multiple sensors may provide more precise gait measurements, the calculations become increasingly more computationally expensive with more sensors because there is much more data to analyze and more (or more powerful) processors are required. As with the video capture systems, these systems provide more data than would be needed for a typical treating clinician. These systems also require significant modifications to the treadmill to allow for the installation of the instrumented deck. 
     A third version uses one or more force plates positioned directly below the treadmill belt which sit atop force sensors to sense the load on the treadmill belt as it is transferred to the force plates. Force plate construction is somewhat disadvantageous in that it causes uncertainty in the gait measurements because of friction and vibration between the belt and the force plates. Friction is notoriously difficult to compensate for in gait calculations, due in part to its variability and multi-dimensional effects. In addition, as with the instrumented deck version, significant modifications are needed to implement this type of gait measuring system on an existing treadmill. 
     Treating therapists typically do not have time to set up a complicated gait recording system, nor can they spend significant money to do so. They also do not need a system that provides an abundance of data—just a few simple parameters that can be compared over time to assess a patient&#39;s gait and progress. Given that treadmills are common equipment for rehabilitation clinicians, it would be advantageous to use clinicians&#39; treadmills to measure gait parameters. 
     Therefore, it is an object of this invention to provide a relatively low cost, simple gait-recording system that provides appropriate gait parameters that can be used daily in the clinic. It is another object to provide a gait measurement system that can be easily retrofitted to a therapist&#39;s existing treadmill. 
     SUMMARY OF THE INVENTION 
     This gait analysis apparatus comprises three, and preferably four, vertical force sensors disposed between a treadmill and the ground. When a person walks on the treadmill belt, each force sensor emits an electronic signal proportional to the load on the frame. The sensors measure the load hundreds of times per second and that data, in combination with the speed of the treadmill belt, enables a processing unit to calculate many gait parameters. The resultant calculations are displayed to the clinician in numeric and graphical formats. Due largely to the few number of force sensors, the apparatus is relatively inexpensive compared to existing gait parameter apparatuses and can be easily retrofitted to existing treadmills by either replacing the treadmill&#39;s existing ground supports with force sensors or resting the treadmill on top of a frame that has integral force sensors. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG. 1  is a top perspective view of a treadmill with the gait apparatus attached. 
         FIG. 2  is a bottom perspective view of the treadmill of  FIG. 1 . 
         FIG. 3  is a cut-away side view of a load cell in a housing. 
         FIG. 4  is a cut-away side view of the rear housing showing the two load cells and feet. 
         FIG. 5  is a sample display of a patient&#39;s gait parameters. 
         FIG. 6  illustrates the relative positions of force sensors in a rectangular arrangement. 
         FIG. 7  illustrates the relative positions of force sensors in a triangular arrangement. 
         FIG. 8  shows a treadmill resting atop a frame. 
         FIG. 9  shows a frame with force sensors in housings and feet. 
     
    
    
     DETAILED DESCRIPTION OF THE INVENTION 
       FIGS. 1 and 2  illustrate the gait analysis apparatus in which force sensors  12  in housings  16  and  17  are disposed between the treadmill base  11  and the ground. In the preferred embodiment an adjustable foot  15  is disposed between each force sensor and the ground, as shown in  FIGS. 3 and 4 . An endless treadmill belt  14  is connected to the base  11 , typically over at least two rollers within the base  11 . The belt  14  has an upper surface which serves as walking surface for the patient. When the patient walks on the belt  14  the load is transferred to the base  11 , which in turn causes each force sensor  12  to emit an electronic signal proportional to the load on the base  11 . 
     The load of the treadmill plus the patient is transferred through the force sensors  12  to the adjustable foot  15 , then to the ground. Each force sensor  12  senses the change in the load and transmits a signal proportional to the load to a receiver  20  which in turn transmits the signal to one or more processing units  22 . The speed of the treadmill belt is measured as either a digital pulse or actual scalar value. Most treadmills have a simple method for measuring speed for feedback, be it through signals emitted from a magnetic sensor and embedded magnets in the roller pulley or an encoder directly on the motor providing servo feedback. These signals are all simply a digital pulse that occurs a certain number of times per rotation of the motor. Another less sophisticated but nonetheless functional option is to place an optical reflective sensor in the treadmill and paint or stick reflective marks on a rotating component and measure the time between signal pulses generated by the sensor. Regardless of method to measure speed, the present system measures time between signal pulses and divides a treadmill-specific constant by this number to obtain speed. 
     This system will inherently have three functions: measurement, data acquisition, and processing. Discrete and integrated circuits may be employed. The measurement is accomplished by the force sensors and speed sensor. The data acquisition takes the sensor signals and translates them into something that can be interpreted by a computer, in this case converting the analog signal to digital. This may also include filtering and amplification of the signal. The processing performs the gait analysis and hosts the user interface. Communications may be made by wire or wirelessly. Preferably these communications are made wirelessly via USB, Bluetooth, or other wireless communication protocol. 
     Software installed on host system uses the load data and speed of the treadmill belt  14  to calculate a multitude of common gait parameters including step length, stride length, symmetry, swing and stance phase percentages. The system measures static load at the center of pressure on each foot at hundreds of times per second, approximating real-time movement measurements. After subtracting the load of the system without the patient, i.e. the tare load, the load values and the known geometry of the sensor locations are used to calculate the location and magnitude of the center of pressure for each data point. Static analysis principles are used to calculate the gait parameters. For example, the ratio of the sum of the front load measurement(s) minus the sum of the rear load measurements, divided by the sum of all load measurements gives a single static load data point. In a preferred embodiment, force sensor and speed sensor data is acquired at a rate of 250 data points per second. In a specific embodiment, the force sensors  12  output a small voltage that changes relative to the load on them. Those signals are transmitted to a data acquisition board which amplifies and filters them, and then converts them to digital values. This is preferably performed by a microprocessor which also reads the digital pulse from the speed sensor and measures the time between consecutive pulses. The data acquisition board is connected to a host system, such as a tablet, computer, smartphone, or other device having one or more processors. Software installed on the host system dues additional; computation and analysis using the force sensor and speed data. 
     The unique pattern created by the center of pressure during gait is analyzed to determine the occurrence and location in both time and two-dimensional space of the four distinct gait events: heel strike and toe off for each foot.  FIG. 5  shows a display  18  of certain parameters measured by the apparatus, including swing phase time, step length, total weight bearing, base of support, and a map of the center of pressure through the gait cycle, referred to herein as a gait pattern. This can be accomplished in various ways by observing the deviation of the location of the center of pressure during these events. For instance, when only one foot is in contact with the treadmill belt and the other is in swing phase, the lateral movement of the center of pressure is limited to the width of the footprint and is therefore small in velocity. At the same time, coronal movement is approximate to the speed of the treadmill belt, with only the transition of load from the heel to the ball to the toe causing minor deviation from it. Upon heel strike of the opposing foot, the center of pressure immediately shifts quickly away from the stance foot in one or both directions, depending on the user&#39;s gait. Similarly, upon toe off of the first foot, the angular velocity immediately stabilizes to the confines of the opposing foot as previously described. Both deviations can be monitored independently, such as via differentiation, or correlatively. The latter can be done by calculating the direction of the velocity vector of the center of pressure. Once an event is deemed to have occurred within a window, the precise location and timing of the event is estimated by searching this window of data points for the exact location of the substantive change in direction. This method has the advantage of being able to detect events even in the case of some crossover or short-stepping, making it ideal for analyzing asymmetric gait. Once the location and timing of heel strike and toe off for each foot are known, a complete analysis of gait parameters can be performed on the data. 
     Any form of force sensor may be utilized. Preferably a cantilever beam-style strain gauge is used, as shown in  FIGS. 3 and 4 , and these are available commercially. The force sensors  12  are rigidly connected to each other. Typically four force sensors are employed, arranged in a rectangle, as shown in  FIG. 6  in which the dashed rectangle indicates the relative placement of the sensors. The apparatus will also work with three force sensors arranged in a triangle as shown in  FIG. 7  in which the dashed triangle indicates the relative placement of the sensors. The three-sensor arrangement is less expensive, but suffers the potential of reduced accuracy and precision, as well as increasing the risk that the treadmill will tip over because the center of the load might fall outside the triangle. If three sensors are used it&#39;s preferable to locate the force sensors well beyond the perimeter of the treadmill walking surface. However, given the sensitivity of current force sensors, the reduction in accuracy and precision is not material to the success of therapy and rehabilitation. 
     The apparatus can be implemented in several configurations. In one, force sensors are integrated directly into the base of the treadmill, a configuration most commonly used for new gait apparatuses. In this configuration one end of the force sensor  12  is mounted to the treadmill base  11  and the other end of the force sensor is attached to the adjustable foot  15  that rests on the ground. The adjustable feet are used to level the treadmill, as known in the art. 
     In another configuration, modular attachments that house the force sensors are attached to the treadmill base  11 , preferably using mounting points that already exist on the base for the ground support. Additional mounting points may be made in the base to provide additional stability and durability, if necessary. There are two types of housings: one housing  16  holds a single force sensor, as shown in  FIG. 3 , and a second housing  17  holds two force sensors, as shown in  FIG. 4 . The single-sensor housings  16  are typically used in the front of the treadmill, one on each side of the mechanism that elevates the head of the treadmill belt to create an inclined walking surface. The dual-sensor housings  17  are typically used across the rear of the treadmill where there&#39;s no treadmill structure to straddle. 
     A third configuration employs an adjustable stand-alone frame  19  that has force sensors  12  in housings  16  and  17  and feet  15  attached to each housing. See  FIG. 9 . A treadmill is placed on top of the frame  19  and secured to it. In practice, the ground supports of the treadmill are typically removed before the treadmill is placed atop the frame  19 .  FIG. 8  shows a treadmill sitting atop a frame  19 . 
     While there has been illustrated and described what is at present considered to be the preferred embodiment of the present invention, it will be understood by those skilled in the art that various changes and modifications may be made and equivalents may be substituted for elements thereof without departing from the true scope of the invention. Therefore, it is intended that this invention not be limited to the particular embodiment disclosed, but that the invention will include all embodiments falling within the scope of the appended claims.