Patent Publication Number: US-2020281300-A1

Title: Chronic Traumatic Encephalopathy Limiting Sports Helmet

Description:
CROSS REFERENCE TO RELATED APPLICATIONS 
     Not Applicable. 
     BACKGROUND OF THE INVENTION 
     The present invention relates to helmets, and more particularly to a sports helmet that utilizes microprocessor controlled valves and re-inflatable bladders for reducing head impact in the helmet and configured for customizable operation. 
     The present invention is an improvement in headgear or helmets for high impact sports such as football, lacrosse, or any other sport where potential head injury can occur. Previous attempts at reducing such injuries have resulted in helmets with more internal cushioning, advanced materials, or design of the shell to withstand impact. These solutions fail to significantly diminish the G forces that are repeatedly experienced by football players during practice and games, which are the leading cause of chronic traumatic encephalopathy in athletes. Further, prior attempts to create injury reducing helmets were not configurable for a particular user, or useable repeatedly during play. 
     BRIEF SUMMARY OF THE INVENTION 
     A primary advantage of the invention is to provide a helmet and method of reducing head injury in high impact sports. 
     Another advantage of the invention is to provide a customizable helmet that operates based on collected data for a particular user. 
     Yet another advantage of the invention is to provide a helmet with re-inflatable bladders to cushion head impact within the helmet. 
     Still yet another advantage of the invention is to provide a software collection system of impacts to permit fine-tuning of the bladder, valve and microprocessor control of the helmet. 
     Yet another advantage of the invention is to provide an immediate resettable helmet system that can be used over and over during play. 
     In accordance with a preferred embodiment of the present invention, there is shown a smart helmet for protection of head injury in contact sports having a hard shell defining a compartment for receiving a portion of a wearer&#39;s head, the shell having an interior surface and an exterior surface, a plurality of inflatable bladders filled with air, the bladders on the interior surface of the shell, a valve disposed on at least one bladder responsive to signals from a controller, at least one flexible extendible strap having a first relaxed state and a second extended state operably engaged to at least one bladder and at least one point on the inside of the helmet, at least one accelerometer attached to the helmet operably connected to the helmet body for sensing g force change on the helmet in operation, at least a second accelerometer operably connected to the wearer&#39;s head for sensing g force change on the wearer&#39;s head in operation, an electrically actuated valve on the bladder responsive to an accelerometer force measurement determined by the controller threshold being met, and the valve, in response to control signals from a controller, exhausts a portion of the air in the bladder to the atmosphere extending the strap to the second state followed by the strap returning to the first state by drawing atmospheric air through the valve and re-inflating the bladder. 
     In accordance with another embodiment of the invention, there is shown a smart helmet for protection of head injury in contact sports having a hard shell defining a compartment for receiving a portion of a wearer&#39;s head, the shell having an interior surface and an exterior surface, a plurality of inflatable bladders filled with air, the bladders on the interior surface of the shell, a valve disposed on at least one bladder responsive to signals from a controller, at least one flexible extendible strap having a first relaxed state and a second extended state operably engaged to at least one bladder and at least one point on the inside of the helmet, at least one accelerometer attached to the helmet operably connected to the helmet body for sensing g force change on the helmet in operation, at least a second accelerometer operably connected to the wearer&#39;s head for sensing g force change on the wearer&#39;s head in operation, an electrically actuated valve on the bladder responsive to an accelerometer force measurement determined by the controller threshold being met, and the valve, in response to control signals from a controller, exhausts a portion of the air in the bladder to the atmosphere extending the strap to the second state followed by the strap returning to the first state by drawing atmospheric air through the valve and re-inflating the bladder. 
     In accordance with another preferred embodiment of the invention there is shown a smart helmet for protection of head injury in contact sports having a hard shell defining a compartment for receiving a portion of a wearer&#39;s head, the shell having an interior surface and an exterior surface, a plurality of inflatable bladders filled with air, each bladder positioned on the interior surface of the shell, a valve disposed on each bladder responsive to signals from a controller, a memory containing material in at least one bladder that re-inflates the bladder after an impact event by drawing atmospheric air through the valve, a least one accelerometer attached to the helmet operably connected to the helmet body for sensing acceleration change on the helmet in operation, at least a second accelerometer operably connected to the wearer&#39;s head for sensing g force change on the wearer&#39;s head in operation, an electrically actuated valve on the bladder responsive to an accelerometer measurement determined by the controller threshold being met; and where the controller produces a signal and the controller activates a motor by electrical power to one or more valves to an open state to expel air, and turns off electrical power to return the valves to a closed state. 
     Other objects and advantages will become apparent from the following descriptions, taken in connection with the accompanying drawings, wherein, by way of illustration and example, preferred embodiments of the present invention are disclosed. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG. 1  is a side schematic view of a helmet having an internal air cushion bladder(s) according to a preferred embodiment of the invention. 
         FIG. 2  is a graph showing Pressure vs. Head Displacement with an initial velocity of 13 ft/sec for a 1, 2 and 4 inch bladder height with y axis from 0 to 100 psig. 
         FIG. 3  is a graph showing Pressure vs. Head Displacement with an initial velocity of 13 ft/sec for a 1, 2 and 4 inch bladder height with y axis from 0 to 120 psig. 
         FIG. 4  is a graph showing Acceleration vs. Head Displacement in Helmet with an initial velocity of 13 ft/sec for a 1, 2 and 4 inch bladder height with no pressure relief valve. 
         FIG. 5A  is graph showing Acceleration vs. Head Displacement in Helmet for a 1 inch bladder height in a helmet with y axis from 0 to 300 g forces. 
         FIG. 5B  is graph showing Acceleration vs. Head Displacement in Helmet for a 2 inch bladder height in a helmet with y axis from 0 to 100 g forces. 
         FIG. 5C  is graph showing Acceleration vs. Head Displacement in Helmet for a 4 inch bladder height in a helmet with y axis from 0 to 100 g forces. 
         FIG. 6  is a graph showing Maximum Acceleration vs. Helmet Size in inches for an initial velocity of 13 ft/sec. 
         FIG. 7  is a graph showing Maximum Acceleration vs. Initial Velocity for a 4 inch bladder height. 
         FIG. 8  is a graph showing Maximum Acceleration vs. Initial Velocity for different typical NFL players and their speed before impact. 
         FIG. 9  is a side schematic of a helmet with microcontroller, accelerometers, and air cushioned bladders according to a preferred embodiment of the invention. 
         FIG. 10  is a schematic showing a cylindrical valve activated by an electric motor for releasing air pressure according to a preferred embodiment of the invention. 
         FIG. 11  is a flow chart of the operation of the helmet according to a preferred embodiment of the invention. 
         FIG. 12  is a block diagram of the main components of the helmet system according to a preferred embodiment of the invention. 
         FIG. 13  is a side schematic view of a helmet with bladder and straps in a contracted state according to a preferred embodiment of the invention. 
         FIG. 14  is a side schematic view of a helmet with bladder and straps in an extended state according to a preferred embodiment of the invention. 
         FIGS. 15A and 15B  are side schematic views of a helmet with bladder and straps in a contracted and extended state according to a preferred embodiment of the invention. 
         FIG. 16  is a flow chart of customized and optimized size and bladder design for a helmet according to a preferred embodiment of the invention. 
         FIG. 17  is a flow chart of customized and optimized post hit processing software or firmware with annual updating for a helmet according to a preferred embodiment of the invention. 
     
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
     Detailed descriptions of the preferred embodiments are provided herein. It is to be understood, however, that the present invention may be embodied in various forms. Various aspects of the invention may be inverted, or changed in reference to specific part shape and detail, part location, or part composition. Therefore, specific details disclosed herein are not to be interpreted as limiting, but rather as a basis for the claims and as a representative basis for teaching one skilled in the art to employ the present invention in virtually any appropriately detailed system, structure or manner. 
     The drawings constitute a part of this specification and include exemplary embodiments to the invention, which may be embodied in various forms. It is to be understood that in some instances various aspects of the invention may be shown exaggerated or enlarged to facilitate an understanding of the invention. 
     Preferred embodiments of the present invention involve a number of innovations and use of microprocessor control to create an active, smart helmet configurable to an individual&#39;s physical dimensions, as well as their response to repeated head impacts through data collection by the helmet. 
     The impact on a player&#39;s head in a helmet with an air bladder cushion is generally shown by the following basic physics: 
     With initial velocity of player, when helmet is stopped, the player&#39;s head moves inside the helmet compressing the cushion material. The cushion exerts a decelerating force on the head according to the compression of the cushion, F=ma. 
     As the cushion material compresses, the force on the player&#39;s head increases as shown F=f(x). Deceleration increases as cushion is compressed a=f (x)/m. For fixed mass and spring constant, g&#39;s increase linearly with head displacement for most cushioning materials. 
     It has been observed that the following occurs with respect to helmet impacts: The higher the initial velocity for a given helmet height, the higher the max g&#39;s experienced; larger helmets limit max g&#39;s experienced; clamping the max pressure limits max g&#39;s but also extends head travel; to globally limit the max g&#39;s experienced, the clamping pressure must be adjusted for each head mass and initial velocity/helmet deceleration; and using the smart helmet concept to limit pressure according to initial velocity significantly reduces g forces experienced by a player. 
     According to a preferred embodiment of the invention, a helmet is provided that utilizes a multi-valved bladder under microprocessor control that opens one or more of the valves upon a certain level of g force impact or other displacement as sensed by on-board accelerometers. One or more bladders are operably connected to one or more valves that instantly open upon a signal from the microprocessor to relieve the bladder pressure and slow down head displacement in a safer and more controlled manner. The bladder may be made of a material that re-inflates itself due to internal structure or other means such as a small fan or motor controlled by the microprocessor or by straps that apply negative bias against the bladder so as to re-inflate after activation. The helmet would also be configured to accommodate the locations of different bladders of various shapes located in areas of most concern and the helmet may take on a more oval shape with higher central crown from top to bottom of the helmet. Data of previous impacts may be recorded and can be used to activate the bladder upon different impact profiles as determined by the processor. 
     Turning now to  FIG. 1  there is shown a side schematic view of helmet  100  with hard shell  105  having in internal generally compressible bladder  110  with height  115  in an initial state. User has head  125  placed in contact with bladder  110  which upon impact has displacement direction  120 . As will be more fully described below, bladder  110  cushions head  125  in displacement direction  120  to decelerate head  125 . Bladder  110  may preferably be filled with open celled foam, or memory foam or have chambers that are filled with gas, air, or other fluid. 
     Turning now to  FIG. 2  there is shown a graph  200  showing Pressure vs. Head Displacement with an initial velocity of 13 ft/sec for a 1, 2 and 4 inch bladder height with y axis from 0 to 100 psig. Line  215  shows displacement in inches versus pressure in pounds per square inch for a bladder height of 1 inch. Line  220  shows displacement  210  in inches versus pressure  205  in pounds per square inch for a bladder height of 2 inches. Line  225  shows displacement in inches versus pressure in pounds per square inch for a bladder height of 4 inches. 
     Turning now to  FIG. 3  there is shown a graph showing Pressure vs. Head Displacement with an initial velocity of 13 ft/sec for a 1, 2 and 4 inch bladder height with y axis from 0 to 120 psig. Pressure  305  is graphed against displacement  310  for the different bladder heights, with line  315  showing bladder height 1 inch, line  320  showing bladder height 2 inches, and line  325  showing bladder height 4 inches. Displacement  310  in inches shows the movement of a user&#39;s head and related pressure in pounds per square inch for each bladder height. 
     Turning now to  FIG. 4  there is shown graph  400  showing Acceleration  405  vs. Head Displacement  410  with an initial velocity of 13 ft/sec for a 1, 2 and 4 inch bladder height with no pressure relief valve. Line  415  depicts the curve for a 1 inch bladder, line  420  depicts a curve for a 2 inch bladder, and line  425  depicts a curve for a 4 inch bladder. 
     Turning now to  FIG. 5A  there is shown graph  500  showing Acceleration vs. Head Displacement for a 1 inch bladder height in a helmet with y axis  505  from 0 to 300 g forces. X axis  510  is head displacement in inches. Line  515  shows g force acceleration at an initial velocity of 13 feet/sec with no pressure relief. Line  520  shows acceleration with a maximum pressure relief of 22.8 psig with line  525  the point of maximum allowable displacement of 1 inch due to the bladder size. This demonstrates that with a 1 inch bladder, and a 13 feet/sec initial velocity, g forces of 57 g&#39;s are possible where line  525  crosses line  520 . Line  535  shows that with pressure relief at 4.5 psig, a maximum acceleration of 11 g&#39;s would be possible, except that the head is traveling further than the bladder height, so this is not possible. 
     Turning now to  FIG. 5B  there is shown a graph  550  showing Acceleration vs. Head Displacement for a 2 inch bladder height in a helmet with y axis  555  from 0 to 100 g forces. X axis  560  is head displacement in inches. Line  570  shows g force acceleration at an initial velocity of 13 feet/sec with no pressure relief. Line  580  shows acceleration with a maximum pressure relief of 18 psig with line  585  intersecting at displacement of 2 inches the point of maximum allowable displacement due to the bladder size. This demonstrates that with a 2 inch bladder, and a 13 feet/sec initial velocity, g forces of 20 g&#39;s are possible where line  585  crosses line  595 , the maximum possible displacement due to the bladder height of 2 inches. 
     Turning now to  FIG. 5C  there is shown graph  551  showing Acceleration vs. Head Displacement for a 4 inch bladder height in a helmet with y axis  556  from 0 to 100 g forces. X axis  561  is head displacement in inches. Line  571  shows g force acceleration at an initial velocity of 13 feet/sec with no pressure relief. Line  591  shows acceleration with a maximum pressure relief of 4 psig with line  591  intersecting at bladder height line  596  after allowable displacement due to the larger bladder size of 4 inches. This demonstrates that with a 4 inch bladder, and a 13 feet/sec initial velocity, g forces are limited to 10 g&#39;s and are contained. 
     Turning now to  FIG. 6  there is shown a graph  600  showing Maximum Acceleration on y axis  605  vs. Helmet Size in inches on x axis  610  for an initial velocity of 13 ft/sec. Line  615  shows as helmet bladder size 610 increases, maximum acceleration from an initial velocity of 13 ft/sec  605  decreases. 
     Turning now to  FIG. 7  there is shown a graph  700  showing Maximum Acceleration on y axis  705  vs. Initial Velocity on x axis  710  for a 4″ bladder height. Line  715  shows that as initial velocity  710  increases, with a 4 inch bladder height, head acceleration  705  increases. 
     Turning now to  FIG. 8  there is shown graph  800  with Maximum Acceleration on y axis  805  vs. Initial Velocity on x axis  810  for different typical NFL players and their speed before impact represented by lines  820 ,  825 ,  830  and  835 . Line  840  shows increasing head acceleration as initial velocity increases with a 4 inch bladder, and as the faster players shown in line  835  are involved in an impact, they do not exceed the concussion threshold line  815  since the maximum head acceleration line  840  crosses line  835  well below line  815 , the concussion threshold. The higher the initial velocity  810 , the higher the maximum g forces  805  are experienced for a given helmet height. However, these g forces are well below what would be experienced in the absence of the present invention. Line  845  shows an average game acceleration over multiple impacts. 
     Turning now to  FIG. 9  is a side schematic of helmet  900  having an outer shell  105  with microcontroller  935 , helmet shell  105  and head  125 , accelerometers  925  and  930 , respectively and air-cushioned bladder  905  according to a preferred embodiment of the invention. Accelerometer  925  is preferably operably attached to helmet shell  105  and accelerometer  930  is preferably operably connected to head  125 , preferably via head cap  1310  as shown in  FIGS. 13 and 14 . Bladder  905  is shown with bladder height  950  which reduces acceleration of impacts as the size increases. Upon impact, bladder  905  receives force from the user&#39;s head  125  as it moves toward shell  105  causing microcontroller  935  upon receiving acceleration and pressure signals from accelerometers  925  and  930  and pressure sensors  936  disposed in bladder  905 , signals to motor  1030  ( FIG. 10 ) that electrically powers valves  940  to open and permit air to expel from bladder  905  when certain threshold pressure and/or acceleration limits are reached. Pressure sensors  936  are operably connected to microcontroller  935  that receives pressure readings. Once the impact event has ended as determined by the accelerometers and pressure sensors signaling to the microcontroller, valves  940  permit air to flow back into the bladder and re-inflate as further described below. The microcontroller or other storage device may transmit via Bluetooth® or other wireless protocol all acceleration and bladder pressure data totals to a storage device on the sidelines. 
     Turning now to  FIG. 10  is a schematic showing cylindrical valve  1000  activated by electric motor  1030  that receives current from the microcontroller and from the battery, thereby alternating the magnetic field in windings  1050  through lines  1060  and  1065 . As the electric current is applied to the winding  1050  of motor  1030 , attached to the valve  1000 , the valve rotates aligning the core  1005  with opening  1010  on the valve to permit airflow  1015  through valve  1000 . When the current is turned off, the helical spring  1020  returns the valve to its closed position. 
     Turning now to  FIG. 11  is a flow chart of the operation of the helmet according to a preferred embodiment of the invention. The flow begins with football hit  1105  that is sensed by helmet accelerometers that read the magnitude and direction of the helmet and head deceleration in box  1110 . Box  1115  shows the microcontroller computing the optimum pressure to minimize head acceleration within the helmet envelop. Box  1120  shows where the head accelerometer begins logging magnitude and direction of player&#39;s head acceleration, and in box  1125  pressure sensors in each segment of the helmet bladder begin logging pressure data. Box  1113  shows that when pressure reaches an optimum limit, the microcontroller begins to open the valves to maintain no more than a maximum pressure. Box  1135  the head accelerometer logs the magnitude and direction of head g forces and modulates which valves to open or close accordingly. Box  1140  shows when the head accelerometer shows head g forces below a pre-determined threshold, the valves remain open all the way to re-inflate the bladder with elastic bands or other mechanism in the helmet and the process ends at block  1145 . 
     Turning now to  FIG. 12  is a block diagram  1200  of the main components of the helmet system according to a preferred embodiment of the invention. Block  1205  is individual player customized and optimized software and firmware with the potential for annual or other time period updating. Software controls microcontroller  1215  which in turn is operably connected to valves  1242 ,  1244 ,  1246  and  1248 . Microcontroller  1215  is also operably connected to bladder compartments  1232 ,  1234 , and  1236  through valves previously described. Helmet accelerometer  1210  and head accelerometer  1220  are also operably connected to microcontroller  1215 . 
     Turning now to  FIG. 13  is a side schematic view of helmet  1300  with hard shell  105  and attachment  1305  connecting the bladder to an elastic strap  1315  on one side and attached to the helmet at attachment point  1325 . Elastic strap  1315  is shown in a retracted state  1320 . A tight fitting head cap  1310  is worn by the user that connects the head to attachment point  1305 . Contracted state  1320  has a length  1312  that may be of any variety depending on head and helmet sizes or level of impact acceleration desired. 
     Turning now to  FIG. 14  is a side schematic view of helmet  1400  with shell  105  having elastic strap  1315  in an extended state  1316  after impact. As can readily be seen, while impact is occurring, the bladder compresses, air is expelled, and the elastic strap extends. This all occurs in microseconds after impact. 
     Turning now to  FIG. 15  is side schematic views of a helmet  1500  with bladder and straps in a contracted and extended state according to a preferred embodiment of the invention. Bladder  1505  is bonded to the helmet on the inside of shell  105  and attached to head cap  1510 . On each side of head cap  1510  are attachment points for elastic strap  1315  shown in a relaxed state having length  1312  and in extended state  1316  after impact. The elastic straps  1315  may be positioned on the back and both sides of the user&#39;s head area and arranged as shown. After impact, the elastic straps  1315  return the helmet back to a rest position, thereby re-inflating the bladders  1505  by causing the bladder  1505  to draw air through the valves and back into the bladder  1505  as the elastic straps  1315  return to their un-extended shorter state. 
     Turning now to  FIG. 16  is flow chart  1600  of customized and optimized fit and sizing for a helmet according to a preferred embodiment of the invention. At step  1605 , helmet measures are taken for a particular user, specifically at step  1610 , a player&#39;s head front to back, side to side, height above eye level and circumference of the head are measured and recorded. At step  1615 , the player&#39;s maximum running speed and acceleration off a line are measured and recorded. At step  1620 , a calculation for size of helmet is made so that the individual player&#39;s head has sufficient travel distance in all directions of the helmet to limit head g forces to a minimum at a player&#39;s maximum helmet speed and acceleration. Step  1625  has the design for each of the  5  bladders according to the already measured player head size and shape to optimize cushioning in all directions. Step  1630  involves a custom helmet fitting for the player to permit small adjustments of the straps, attachment points, bladder location and size and head cap. 
     Turning now to  FIG. 17  is flow chart  1700  of customized and optimized software or firmware with annual updating for a helmet according to a preferred embodiment of the invention. After a hit is experienced at step  1705 , data is recorded at step  1710  for each bladder pressure and maximum pressure is compared for each bladder with an individual player template for optimum play protocol. Step  1715  logs head acceleration results and are compared with cumulative safety total, with a maximum number of allowable accelerations for a game or season. Step  1725  determines if a single threshold is exceeded, the helmet signals an alarm operably connected to the microcontroller and the player is sidelined and out of the game. Step  1730  logs cumulative accelerations and if a threshold is exceeded the helmet alarms the player and the player is taken out of the game. Step  1735  compares acceleration and pressure data with optimum play style template and the results are fed back into the player via voice instructions in the helmet to modify his style of hit and play. Finally, in step  1740 , via Bluetooth®, the helmet transmits all acceleration and bladder pressure data totals to a storage device on the sidelines and player lifetime CTE log file is created and compares that with the player&#39;s CTE health status to a healthy template for any similarly situated player. A sideline referee can monitor players during the game and make decision of whether a player has incurred too many or too high an impact to continue play. 
     While the invention has been described in connection with a preferred embodiment, it is not intended to limit the scope of the invention to the particular form set forth, but on the contrary, it is intended to cover such alternatives, modifications, and equivalents as may be included within the spirit and scope of the invention as defined by the later issued claims.