Therapeutic support device and apparatus for cerebrospinal fluid dynamics

Abstract

Therapeutic support device, systems, and methods are directed towards optimizing cerebrospinal fluid dynamics in patients and otherwise healthy individuals. In some embodiments, a therapeutic support device may comprise a base, a thigh rest frame supported by the base and a back frame supported by the base. A back support may be attached to the back frame. A headrest may be movable with respect to the back frame about a headrest access. The back support may define a reference plain. They headrest access may be oriented to a front side of the reference plane and the back frame oriented to a second side of the reference plane.

Description

[0001]Z. Grajcar DKT. NO.408439-X Therapeutic Support Device and Apparatus for Improved Cerebrospinal Fluid Dynamics CROSS-REFERENCE TO RELATED APPLICATIONS The instant application claims priority to U.S. Prov. Pat. App. No.63 / 652,665, entitled THERAPEUTIC SUPPORT DEVICE, filed May 28, 2024. The instant application claims priority to U.S. Prov. Pat. App. No.63 / 652,673, entitled Devices, Systems, and Methods Configured for Optimizing Glymphatic Clearance of the Central Nervous System, filed May 28, 2024. This application claims priority to U.S. Prov. Pat. App. No.63 / 710,018, entitled Pioneering Balanced Treatments for Alzheimer’s Disease, filed October 21, 2024. The above- identified applications are incorporated herein by reference in their entirety into the instant application. SUMMARY Without limiting the scope of the disclosure, a brief summary of some of the claims is set forth below. Additional details of the summarized claims may be found in the Detailed Description below. A brief abstract of the technical disclosure in the specification is provided as well only for the purpose of complying with 37 C.F.R.1.72. There is provided a therapeutic support device comprising: a frame; a back support attached to the frame; and a headrest moveable with respect to the back support about a headrest axis; the back support defining a reference plane, the headrest axis oriented to a first side of the reference plane, the frame oriented to a second side of the reference plane. The therapeutic support may comprise a headrest actuation mechanism arranged to move the headrest about the axis. The therapeutic support may comprise a drive mechanism arranged to transfer force from the headrest actuation mechanism to the headrest. The drive mechanism may comprise a crank arm pivotable with respect to a drive linkage. The drive linkage may be attached to the headrest at a location offset from the headrest axis. The drive mechanism may comprise a belt. The headrest may be moveable about the headrest axis between a first position and a second position. The second position may be rotated at least 90 degrees with respect to the first position. The therapeutic support may comprise a pressure pad moveable with respect to the back support. The pressure pad may be arranged to move along a linear axis oriented orthogonal to the reference plane. Z. Grajcar DKT. NO.408439-X There is also provided a therapeutic support device comprising: a base; a seat frame supported by the base; a back frame supported by the base; a back support attached to the back frame; and a headrest moveable with respect to the back frame about a headrest axis; the back support defining a reference plane, the headrest axis oriented to a first side of the reference plane, the back frame oriented to a second side of the reference plane. The back frame may comprise a first portion supported by the base and a second portion moveable with respect to the first portion, the headrest supported by the second portion. The therapeutic support device may comprise an adjustment mechanism arranged to move the second portion with respect to the first portion. The back frame may comprise a third portion moveable with respect to the second portion. The device may comprise a pressure pad supported by the third portion. The therapeutic support device may comprise an adjustment mechanism arranged to move the third portion with respect to the second portion. The back frame may be pivotable with respect to the seat frame about a hinge. The therapeutic support device may comprise an adjustment mechanism attached to the seat frame and attached to the back frame. The seat frame may be pivotable about the hinge with respect to the base. The therapeutic support device may comprise an adjustment mechanism attached to the seat frame and attached to the base. There is also provided a therapeutic support device comprising: a back support and a headrest defining a treatment area; the headrest moveable with respect to the back support about a headrest axis, the axis extending through the treatment area. The therapeutic support device may be arranged to move in an oscillatory motion comprising a first movement and a second movement. The first movement may comprise moving from a first treatment position to a second treatment position. The second movement may comprise moving from the second treatment position to the first treatment position. The first movement may comprise a first time period and the second movement may comprise a second time period. The second time period may be longer than the first time period. The first time period may comprise 5 seconds and the second time period may comprise 7 seconds. The first time period may comprise 35%-45% of a total time period and the second time period may comprise 55%-65% of the total time period. Z. Grajcar DKT. NO.408439-X There is also provided an apparatus comprising: a support surface configured to support a subject, wherein rotating oscillation of the support surface between a first treatment position and a second treatment position is configured to change cerebrospinal fluid (CSF) dynamics of the subject. The apparatus may further comprise: a fulcrum about which the support surface is configured for the rotating oscillation. The fulcrum may be configured to rotate a first end of the support surface relative to a second end of the support surface. The fulcrum may be located in a middle of a distance from the first end to the second end. The fulcrum may be located 50% of a distance from the first end to the second end. The fulcrum may be located 40% of a distance from the first end to the second end. The fulcrum may be located at a position between the first end to the second end, inclusive. The apparatus may further comprise: a motor configured to rotate the support surface about the fulcrum. The motor may be coupled to the fulcrum. The motor may be located at the fulcrum. The apparatus may further comprise: a support member coupled to the support surface. The motor may be configured to move the support member relative to the support surface to rotate the support surface about the fulcrum. The motor may be characterized as a first motor, further comprising: a support member coupled to the support surface; and a second motor coupled to the support member. The second motor may be configured to move the support member relative to the support surface to rotate the support surface about the fulcrum. The apparatus may further comprise: a leg configured to oscillate a length by extending and retracting the leg relative to a supporting surface to rotate the support surface. The leg may be characterized as a first leg and the length may be characterized as a first length, further comprising: a first end of the support surface; a second end of the support surface that is opposite the first end of the support surface; and a second leg configured to oscillate a second length by extending and retracting the second leg relative to the supporting surface to rotate the support surface. The first leg may be closer to the first end of the support surface than the second end of the support surface. The second leg may be closer to the second end of the support surface than the first end of the support surface. The first leg may be configured to oscillate the first length by extending and retracting the first leg relative to the supporting surface while the second leg may be configured to oscillate the Z. Grajcar DKT. NO.408439-X second length by retracting and extending the second leg relative to the supporting surface, synchronously. The first length and the second length may be different lengths. An axis of the rotating oscillation of the support surface may be configured to coincide with a center of gravity for the subject. The support surface may be 16 degrees up in the first treatment position from horizontal defined by a supporting surface that supports the support surface. A head of the subject may be configured to be 16 degrees up from the horizontal in the first treatment position. The support surface may be from 10 to 20 degrees up in the first treatment position from horizontal defined by a supporting surface that supports the support surface. A head of the subject may be configured to be 10 to 20 degrees up from the horizontal in the first treatment position. The apparatus may further comprise: a control system configured to control the rotating oscillation. The control system may be configured to execute a velocity profile for acceleration and deceleration during the rotating oscillation to ease transition from movement towards the first treatment position to the second treatment position and vice versa. There is also provided a method comprising: rotating oscillation of a support surface configured to support a subject between a first treatment position and a treatment second position is configured to change cerebrospinal fluid (CSF) dynamics of the subject. The rotating oscillation of the support surface may be configured to rotate a head of the subject from above and below horizontal defined by a supporting surface that supports the support surface. The rotating oscillation of the support surface may be configured to rotate a head of the subject upward. The rotating oscillation of the support surface may be configured to rotate a head of the subject downward. There is also provided an apparatus comprising: an upper body support surface configured to support a back and a head of a subject, wherein rotating oscillation of the upper body support surface between a first treatment position and a treatment second position is configured to change cerebrospinal fluid (CSF) dynamics of the subject. Z. Grajcar DKT. NO.408439-X The apparatus may further comprise: a thigh rest configured to support a thigh of the subject, wherein the upper body support surface is coupled to the thigh rest and configured to rotate in relation to the thigh rest. The apparatus may further comprise: a leg rest configured to support a leg of the subject, wherein the leg rest is coupled to the thigh rest and configured to promote flexion of a knee of the subject. The apparatus may further comprise: a leg rest configured to support a leg of the subject, wherein the leg rest is coupled to the thigh rest and configured to rotate in relation to the thigh rest. The upper body support surface may be 16 degrees up in the first treatment position from horizontal defined by a supporting surface that supports the support surface. The head of the subject is configured to be 16 degrees up from the horizontal in the first treatment position. The apparatus may further comprise: a control system configured to control the rotating oscillation. The control system may be configured to execute a velocity profile for acceleration and deceleration during the rotating oscillation to ease transition from movement towards the first treatment position to the second treatment position and vice versa. The upper body support surface may be from 10 to 20 degrees up in the first treatment position from horizontal defined by a supporting surface that supports the support surface. The head of the subject may be configured to be 10 to 20 degrees up from the horizontal in the first treatment position. There is also provided a method comprising: rotating oscillation of an upper body support surface configured to support a back and a head of a subject between a first treatment position and a treatment second position is configured to change cerebrospinal fluid (CSF) dynamics of the subject. The rotating oscillation of the upper body support surface may be configured to rotate the head of the subject from above and below horizontal defined by a supporting surface that supports the upper body support surface. The rotating oscillation of the upper body support surface may be configured to rotate the head of the subject upward above horizontal defined by a supporting surface that supports the upper body support surface. The rotating oscillation of the upper body support surface may be configured to rotate the head of the subject downward above horizontal defined by a supporting surface that supports the upper body support surface. Z. Grajcar DKT. NO.408439-X There is also provided a method of making a pump system for improving glymphatic clearance, which comprises: providing a pump whose activation is configured to flex a cerebrospinal fluid system of a subject; and providing a control system configured to control a volume of the cerebrospinal fluid in the cerebrospinal fluid system or a part thereof. The method may further comprise: providing the control system configured to decrease the volume of the cerebrospinal fluid in the cerebrospinal fluid system of the subject with a condition of increase in the volume of the cerebrospinal fluid in the cerebrospinal fluid system in relation to a normal state. The subject may have one or more of concussion, traumatic brain injury, chronic traumatic encephalopathy, and hydrocephalus. The method may further comprise: providing the control system configured to decrease a volume of an interstitial fluid from a central nervous system of the subject with a condition of increase in the volume of the interstitial fluid in the central nervous system in relation to a normal state. The subject may have one or more of concussion, traumatic brain injury, chronic traumatic encephalopathy, and hydrocephalus. The method may further comprise: providing the control system configured to increase removal of metabolic waste from a central nervous system of the subject with a condition of increase in the metabolic waste in relation to a normal state. The subject may have one or more of Alzheimer’s disease, multiple sclerosis, stroke, chronic traumatic encephalopathy, and Huntington’s disease. The method may further comprise: providing the control system configured to increase removal of metabolic waste in the cerebrospinal fluid system of the subject with a condition of increase in the metabolic waste in relation to a normal state. The subject may have one or more of Alzheimer’s disease, multiple sclerosis, stroke, chronic traumatic encephalopathy, and Huntington’s disease. The method may further comprise: providing the control system configured to increase removal of metabolic waste in interstitial fluid of the subject with a condition of increase in the metabolic waste in relation to a normal state. The subject may have one or more of Alzheimer’s disease, multiple sclerosis, stroke, chronic traumatic encephalopathy, and Huntington’s disease. Z. Grajcar DKT. NO.408439-X The method may further comprise: providing the control system configured to remove toxins from central nervous system of the subject. The subject may have one or more of chemotherapy, drug overdose, alcohol overdose, and Wernicke-Korsakoff syndrome. The method may further comprise: providing the control system configured to remove toxins from the cerebrospinal fluid of the subject. The subject may have one or more of chemotherapy, drug overdose, alcohol overdose, and Wernicke-Korsakoff syndrome. The method may further comprise: providing the control system configured to remove toxins from interstitial fluid of the subject. The subject may have one or more of chemotherapy, drug overdose, alcohol overdose, and Wernicke-Korsakoff syndrome. The method may further comprise: providing for movement of the pump between a first treatment position and a second treatment position to repeatedly flex the cerebrospinal fluid system. The method may further comprise: providing initiation of the pump configured to flex the cerebrospinal fluid system. The method may further comprise: providing movement of the pump between a first treatment position and a second treatment position to repeatedly flex the cerebrospinal fluid system. The method may further comprise: providing movement of the pump between a first treatment position to a second treatment position in 1 to 10 seconds and the second treatment position to the first treatment position in 1 to 10 seconds in an oscillatory motion. The method may further comprise: providing the movement of the pump between the first treatment position to the second treatment position in 4 to 10 seconds and the second treatment position to the first treatment position in 4 to 10 seconds in the oscillatory motion. The method may further comprise: providing movement the pump between a first treatment position to a second treatment position in an oscillatory motion, wherein the movement from the first treatment position to the second treatment position is configured to cause extension of a spinal segment of the subject and the movement from the second treatment position to the first treatment position is configured to cause flexion of the spinal segment of the subject. The method may further comprise: providing movement the pump between a first treatment position to a second treatment position in an oscillatory motion, wherein the movement from the second treatment position to the first treatment position is a longer time period than the movement from the first treatment position to the second treatment position. Z. Grajcar DKT. NO.408439-X The method may further comprise: providing movement the pump between a first treatment position to a second treatment position in an oscillatory motion, wherein the movement from the second treatment position to the first treatment position is 55% to 65% of time of the oscillatory motion and the movement from the first treatment position to the second treatment position is 35% to 45% of the time of the oscillatory motion. The method may further comprise: providing movement the pump between a first treatment position to a second treatment position in an oscillatory motion, wherein the movement from the second treatment position to the first treatment position is a 7 second period and the movement from the first treatment position to the second treatment position is a 5 second period. There is also provided a method of making a pump system for improving glymphatic clearance, which comprises: providing a plinth whose activation is configured to move cerebrospinal fluid in a subject; and providing a control system to control the plinth to repeatedly move the cerebrospinal fluid. The method may further comprise: providing for tilt of the plinth to and from a home position to repeatedly move the cerebrospinal fluid. The method may further comprise: providing a treatment schedule for the subject to receive 1 to 7 treatment sessions in a week. The method may further comprise: providing the treatment schedule for the subject to receive treatment sessions for 15 minutes or longer. There is also provided a method of using a pump system for improving glymphatic clearance, which comprises: activating a pump configured to flex a cerebrospinal fluid system of a subject; and activating a control system to control the pump to repeatedly flex the cerebrospinal fluid system. The method may further comprise: activating the pump to move to and from a home position to repeatedly flex the cerebrospinal fluid system. The method may further comprise: activating the pump configured to flex the cerebrospinal fluid system. The method may further comprise: activating the pump to move to and from a home position to repeatedly flex the cerebrospinal fluid system. The method may further comprise: activating the pump to move between a first treatment position to second treatment position in 1 to 10 seconds and the second treatment position to the first treatment position in 1 to 10 seconds in an oscillatory motion. Z. Grajcar DKT. NO.408439-X The method may further comprise: activating pump to move between the first treatment position to the second treatment position in 4 to 10 seconds and the second treatment position to the first treatment position in 4 to 10 seconds in the oscillatory motion. The method may further comprise: activating the pump to move between a first treatment position to a second treatment position in an oscillatory motion. Movement from the first treatment position to the second treatment position may be configured to cause extension of a spinal segment of the subject. The movement from the second treatment position to the first treatment position may be configured to cause flexion of the spinal segment of the subject. The method may further comprise: activating the pump to move between a first treatment position to a second treatment position in an oscillatory motion. Movement from the second treatment position to the first treatment position may be a longer time period than the movement from the first treatment position to the second treatment position. The method may further comprise: activating the pump to move between a first treatment position to a second treatment position in an oscillatory motion. Movement from the second treatment position to the first treatment position may be 55% to 65% of time of the oscillatory motion. Movement from the first treatment position to the second treatment position may be 35% to 45% of the time of the oscillatory motion. The method may further comprise: providing movement the pump between a first treatment position to a second treatment position in an oscillatory motion. The movement from the second treatment position to the first treatment position may be a 7 second period. The movement from the first treatment position to the second treatment position may be a 5 second period. There is also provided a method of using a pump system for improving glymphatic clearance, which comprises: activating a plinth configured to move cerebrospinal fluid in a subject; and activating a control system to control the plinth to repeatedly move the cerebrospinal fluid. The method may further comprise: activating the plinth to tilt to and from a home position to repeatedly move the cerebrospinal fluid. The method may further comprise: initiating a treatment schedule for the subject to receive 1 to 7 treatment sessions in a week. The method may further comprise: initiating the treatment schedule for the subject to receive treatment sessions for 15 minutes or longer. Z. Grajcar DKT. NO.408439-X There is also provided a device comprising: an adjustment mechanism configured to position a cerebrospinal fluid pump in a treatment position that fits a subject for treatment cycles of a treatment session; and an actuation mechanism configured for cyclic movement of the cerebrospinal fluid pump between a first treatment position and a second treatment position during the treatment cycles of the treatment session to change cerebrospinal fluid dynamics of the subject. The device may further comprise: a control system configured to control the adjustment mechanism to position the cerebrospinal fluid pump in the treatment position. The device may further comprise: a control system configured to control the actuation mechanism responsive to a heart rate variability of the subject. The device may further comprise: a control system configured to control the actuation mechanism to gait a determined inhalation and exhalation respiratory pattern in the subject. There is also provided a device comprising: an adjustment mechanism configured to position a cerebrospinal fluid pump in a treatment position that fits a subject for treatment cycles of a treatment session; and an actuation mechanism configured for cyclic movement of the cerebrospinal fluid pump between a first treatment position and a second treatment position during the treatment cycles of the treatment session to change cerebrospinal fluid dynamics of the subject, wherein transition from the first treatment position to the second treatment position is configured for inhalation by the subject in transition from the second treatment position to the first treatment position is configured for exhalation by the subject. Inhalation may not start at a regular interval during the treatment session. Exhalation may not start at a regular interval during the treatment session. Exhalation by the subject may be longer than inhalation by the subject. There is also provided a method of using a CSF pump device, the method comprising: providing a CSF pump configured to move a CSF system of a subject and induce change in CSF dynamics of the CSF system; setting up the CSF pump through analyzing respiratory activity, cardiac activity, and brain wave activity of the subject; and starting the CSF pump. The cardiac activity may be related to a heart rate variability of the subject. The brain wave activity may be beta activity brain wave of the subject. The brain wave activity may be delta brain wave activity of the subject. Z. Grajcar DKT. NO.408439-X The respiratory activity may be a respiratory frequency of the subject. The respiratory activity may be inhalation duration and exhalation duration of the subject. The method may further comprise: providing acceleration in an initial part of inhalation followed by deceleration; and providing acceleration in an initial part of inhalation followed by deceleration. There is also provided a method comprising: oscillating a cerebrospinal fluid pump to a distance between a first treatment position and a second treatment position to change cerebrospinal fluid dynamics of a subject. The method may further comprise: moving the cerebrospinal fluid pump the distance from the first treatment position to the second treatment position in a first prescribed time; and moving the cerebrospinal fluid pump the distance from the second treatment position to the first treatment position in a second prescribed time. The method may further comprise: moving the cerebrospinal fluid pump the distance from the first treatment position to the second treatment position at a steady rate defined as the distance divided by the first prescribed time. The method may further comprise: moving the cerebrospinal fluid pump the distance from the second treatment position to the first treatment position at a steady rate defined as the distance divided by the second prescribed time. The method may further comprise: moving the cerebrospinal fluid pump the distance from the first treatment position to the second treatment position with acceleration to a first movement velocity greater than a steady rate defined as the distance divided by the first prescribed time and deceleration to a second movement velocity less than the steady rate. The method may further comprise: moving the cerebrospinal fluid pump the distance from the first treatment position to the second treatment position with a velocity profile characterized as a sinusoidal curve. The sinusoidal curve may represent the velocity during the first prescribed time. The method may further comprise: moving the cerebrospinal fluid pump the distance from the first treatment position to the second treatment position with a velocity profile characterized as a sinusoidal curve. The sinusoidal curve may represent a position during the first prescribed time. The method may further comprise: accelerating the cerebrospinal fluid pump in approximately an initial 50% of the first prescribed time. The method may further comprise: decelerating the cerebrospinal fluid pump in approximately a last 50% of the first prescribed time. Z. Grajcar DKT. NO.408439-X The method may further comprise: moving the cerebrospinal fluid pump the distance from the second treatment position to the first treatment position with acceleration to a first movement velocity greater than a steady rate defined as the distance divided by the second prescribed time and deceleration to a second movement velocity less than the steady rate. The method may further comprise: moving the cerebrospinal fluid pump the distance from the second treatment position to the first treatment position in a profile characterized as a leaky integrator. The method may further comprise: accelerating the cerebrospinal fluid pump in approximately an initial one third of the second prescribed time. The method may further comprise: decelerating the cerebrospinal fluid pump in approximately a last two thirds of the second prescribed time. The method may further comprise: setting parameters with velocity that is maximum; and adjusting the velocity to drive acceleration and deceleration of the cerebrospinal fluid pump. The method may further comprise: correcting a trajectory of acceleration to drive the cerebrospinal fluid pump within motor capability. The method may further comprise: accelerating the cerebrospinal fluid pump to an error correction checkpoint. The method may further comprise: adjusting the trajectory of the cerebrospinal fluid pump based on the velocity at the error correction checkpoint. The method may further comprise: accelerating the cerebrospinal fluid pump slower if the velocity is achieved before reaching the error correction checkpoint. The method may further comprise: accelerating the cerebrospinal fluid pump faster if the velocity is achieved after reaching the error correction checkpoint. The method may further comprise: accelerating of the cerebrospinal fluid pump without change if the velocity is achieved at the error correction checkpoint. The method may further comprise: decelerating the cerebrospinal fluid pump slower if the velocity is achieved before reaching the error correction checkpoint. The method may further comprise: decelerating the cerebrospinal fluid pump faster if the velocity is achieved after reaching the error correction checkpoint. The method may further comprise: decelerating of the cerebrospinal fluid pump without change if the velocity is achieved at the error correction checkpoint. The error correction checkpoint may be one of a plurality of error correction checkpoints. The method may further comprise: measuring by the error correction checkpoint accelerating of the cerebrospinal fluid pump. Z. Grajcar DKT. NO.408439-X The method may further comprise: measuring by the error correction checkpoint decelerating of the cerebrospinal fluid pump. The method may further comprise: accelerating the cerebrospinal fluid pump according to an algorithm. The method may further comprise: accelerating the cerebrospinal fluid pump according to look up table information that accounts for time and the distance traveled. The method may further comprise: accelerating the cerebrospinal fluid pump according to look up table information that accounts for time and velocity traveled. The method may further comprise: using a mathematical formula for velocity of the cerebrospinal fluid pump at different times in position of the cerebrospinal fluid pump. The method may further comprise: using a mathematical formula for acceleration of the cerebrospinal fluid pump at different times in velocity of the cerebrospinal fluid pump. The method may further comprise: accelerating the cerebrospinal fluid pump a plurality of times. The method may further comprise: decelerating the cerebrospinal fluid pump a plurality of times. The method may further comprise: accelerating the cerebrospinal fluid pump relative to a treatment position; and negative accelerating the cerebrospinal fluid pump relative to the treatment position. The method may further comprise: decelerating the cerebrospinal fluid pump relative to a treatment position; and negative decelerating the cerebrospinal fluid pump relative to the treatment position. There is also provided an apparatus comprising: a cerebrospinal fluid pump configured to oscillate a distance between a first treatment position and a second treatment position to change cerebrospinal fluid dynamics of a subject. The cerebrospinal fluid pump may be configured to move the distance from the first treatment position to the second treatment position in a first prescribed time. The cerebrospinal fluid pump may be configured to move the distance from the second treatment position to the first treatment position in a second prescribed time. The cerebrospinal fluid pump may be configured to move the distance from the first treatment position to the second treatment position at a steady rate defined as the distance divided by the first prescribed time. Z. Grajcar DKT. NO.408439-X The cerebrospinal fluid pump may be configured to move the distance from the second treatment position to the first treatment position at a steady rate defined as the distance divided by the second prescribed time. The cerebrospinal fluid pump may be configured to move the distance from the first treatment position to the second treatment position with acceleration to a first movement velocity greater than a steady rate defined as the distance divided by the first prescribed time and deceleration to a second movement velocity less than the steady rate. The cerebrospinal fluid pump may be configured to move the distance from the first treatment position to the second treatment position in a profile characterized as a sinusoidal curve. The acceleration of the cerebrospinal fluid pump may occur in approximately an initial 50% of the first prescribed time. The deceleration of the cerebrospinal fluid pump may occur in approximately a last 50% of the first prescribed time. The cerebrospinal fluid pump may be configured to move the distance from the second treatment position to the first treatment position with acceleration to a first movement velocity greater than a steady rate defined as the distance divided by a second prescribed time and deceleration to a second movement velocity less than the steady rate. The cerebrospinal fluid pump may be configured to move the distance from the second treatment position to the first treatment position in a profile characterized as a leaky integrator. The acceleration may occur in approximately an initial one third of the second prescribed time. The deceleration may occur in approximately a last two thirds of the second prescribed time. The cerebrospinal fluid pump may be a thoracolumbar pump configured to change position of a thoracolumbar spine of the subject. The cerebrospinal fluid pump may be a lumbar pump configured to move a lumbar spine of the subject. The cerebrospinal fluid pump may be a cervical pump configured to move a cervical spine of the subject. The cerebrospinal fluid pump may be characterized as a first cerebrospinal fluid pump, and a second cerebrospinal fluid pump may be a lumbar pump configured to move a lumbar spine of the subject. There is also provided a therapeutic support device comprising: a backrest and a headrest may be configured to define a treatment area; Z. Grajcar DKT. NO.408439-X the headrest may be configured to move with respect to the backrest about a headrest axis, the headrest axis extending through the treatment area. May be arranged to move in an oscillatory motion comprising a first movement and a second movement, the first movement comprising moving from a first treatment position to a second treatment position, the second movement comprising moving from the second treatment position to the first treatment position. Wherein the first movement may comprise a first time period and the second movement comprises a second time period, the second time period being longer than the first time period. Wherein the first time period may comprise 35%-45% of a total time period and the second time period comprises 55%-65% of the total time period. Wherein the cerebrospinal fluid pump may be configured to move the distance from the first treatment position to the second treatment position with acceleration to a first movement velocity greater than a steady rate defined as the distance divided by the first prescribed time and deceleration to a second movement velocity less than the steady rate. a frame attached to the back rest, the backrest defining a reference plane, the headrest axis may be oriented to a first side of the reference plane, the frame may be oriented to a second side of the reference plane a headrest actuation mechanism may be arranged to move the headrest about the headrest axis. Wherein the headrest may be moveable about the headrest axis between a first treatment position and a second position, the second position may be rotated at least 90 degrees with respect to the first treatment position. Wherein the cerebrospinal fluid pump may be configured to move the distance from the first treatment position to the second treatment position in a profile characterized as a sinusoidal curve. Wherein the acceleration may occur in approximately an initial one third of the second prescribed time. Wherein the deceleration may occur in approximately a last two thirds of the second prescribed time. an adjustment mechanism configured to position a cerebrospinal fluid pump in a treatment position that fits a subject for treatment cycles of a treatment session; and an actuation mechanism may be configured for cyclic movement of the cerebrospinal fluid pump between a first treatment position and a second treatment position during the treatment cycles of the treatment session to change cerebrospinal fluid dynamics of the subject. Z. Grajcar DKT. NO.408439-X a control system me be configured to control the adjustment mechanism to position the cerebrospinal fluid pump in the treatment position. a control system may be configured to control the actuation mechanism responsive to a heart rate variability of the subject. There is also provided a method for making a therapeutic support device for improving glymphatic clearance, which comprises: providing a pump whose activation may be configured to flex a cerebrospinal fluid system of a subject; and providing a control system may be configured to control a volume of the cerebrospinal fluid in the cerebrospinal fluid system or a part thereof. providing the control system that may be configured to decrease the volume of the cerebrospinal fluid in the cerebrospinal fluid system of the subject with a condition of increase in the volume of the cerebrospinal fluid in the cerebrospinal fluid system in relation to a normal state. providing the control system may be configured to decrease a volume of an interstitial fluid from a central nervous system of the subject with a condition of increase in the volume of the interstitial fluid in the central nervous system in relation to a normal state. providing the control system may be configured to remove toxins from central nervous system of the subject. There is also provided a therapeutic support device comprising: a backrest and a headrest defining a treatment area; and the headrest may be configured to be moveable with respect to the backrest about a headrest axis, the headrest axis extending through the treatment area. May be arranged to move in an oscillatory motion comprising a first movement and a second movement, the first movement comprising moving from a first treatment position to a second treatment position, the second movement comprising moving from the second treatment position to the first treatment position. Wherein the first movement comprises a first time period and the second movement may comprise a second time period, the second time period being longer than the first time period. Wherein the first time period may comprise 35%-45% of a total time period and the second time period comprises 55%-65% of the total time period. Wherein the headrest may be configured to move a distance from the first treatment position to the second treatment position with acceleration to a first movement velocity greater than a Z. Grajcar DKT. NO.408439-X steady rate defined as the distance divided by a first prescribed time and deceleration to a second movement velocity less than the steady rate. a frame may be attached to the backrest, the backrest defining a reference plane, the headrest axis oriented to a first side of the reference plane, the frame oriented to a second side of the reference plane. a headrest actuation mechanism may arranged to move the headrest about the headrest axis. Wherein the headrest may be moveable about the headrest axis between a first treatment position and a second position, the second position, wherein the headrest is configured to rotate at least 90 degrees with respect to the first treatment position. There is also provided an apparatus comprising: an adjustment mechanism may be configured to position a cerebrospinal fluid pump in a treatment location that fits a subject for treatment cycles of a treatment session; and an actuation mechanism may be configured oscillate the cerebrospinal fluid pump between a distance from a first treatment position and a second treatment position during the treatment cycles of the treatment session to change cerebrospinal fluid dynamics of the subject, wherein the cerebrospinal fluid pump is configured to move the distance from the first treatment position to the second treatment position in a first prescribed time, and the cerebrospinal fluid pump is configured to move the distance from the second treatment position to the first treatment position in a second prescribed time, and the cerebrospinal fluid pump is configured to move the distance from the first treatment position to the second treatment position with acceleration to a first movement velocity greater than a steady rate defined as the distance divided by the first prescribed time and deceleration to a second movement velocity less than the steady rate. Wherein the cerebrospinal fluid pump may be configured to move the distance from the first treatment position to the second treatment position in a profile characterized as a sinusoidal curve. Wherein the acceleration of the cerebrospinal fluid pump occurs in approximately an initial 50% of the first prescribed time. Wherein the cerebrospinal fluid pump may be configured to move the distance from the second treatment position to the first treatment position with acceleration to a first movement velocity greater than a steady rate defined as the distance divided by a second prescribed time and deceleration to a second movement velocity less than the steady rate. Wherein the acceleration may occur in approximately an initial one third of the second prescribed time. Z. Grajcar DKT. NO.408439-X Wherein the deceleration may occur in approximately a last two thirds of the second prescribed time a backrest and a headrest defining a treatment area; and the headrest is configured to be moveable with respect to the backrest about a headrest axis, the headrest axis extending through the treatment area. BRIEF DESCRIPTION OF THE DRAWINGS FIG.1 shows in standard anatomic position a body of an user with a head turned to the left and FIG.2 shows sectional side view of the head supported by a torso. FIG.3 shows the user in supine, which is defined as lying on a back of the user or with the face of the user upward. FIG.4 shows the user in prone, which is defined as having a front of the body of the user 12 with face downward or lying with the chest and the abdomen of a user facing downward. FIG.5 shows a side view of a spine, also known as a spinal column or a vertebral column. FIG.6, along with FIG.5, shows in schematic motion of the spine. FIG.7 shows a side view of brain and upper portion of the spinal cord. FIGS.8-10 shows in schematic view lymphatic vessels, nodes, and organs in humans. FIG.10 shows schematic of how brain metabolic waste and toxins, including lactate, tau and β-amyloid (Aβ) are cleared from the brain. FIG.11-17 show a side view of a cerebrospinal fluid (CSF) pump in accordance with some embodiments which functions and what can arbitrarily be considered a tilt table. FIG.18 shows a schematic representation of a control system. FIG.19 shows a top view of the CSF pump shown in FIGS.11 through 17. FIG.20 shows a schematic timeline for a treatment cycle. FIG.21 shows a schematic timeline for a treatment session. FIGS.22-27 show a side view of the CSF pump in accordance with some embodiments. FIGS.28-30 shows a side view of the CSF pump was with some embodiments. FIGS.31-35 show inside view the CSF pump in accordance with some embodiments. FIG.36 shows a top view of the CSF pump in accordance with some embodiments. FIGS.37-39 shows a side view of the CSF pump of FIG.36. FIG.40 shows a top view of the CSF pump and accordance with some embodiments. FIGS.41-43 show a side view of the CSF pump in FIG.40. FIG.44 shows a bottom view of the CSF pump in accordance with some embodiments. FIG.45 shows a cross-section in side view an example of the CSF pump of FIG.44 at section line 660. Z. Grajcar DKT. NO.408439-X FIGS.46-48 show a side view an example of the CSF pump in accordance with some embodiments. FIG.49 shows an embodiment of a therapeutic support device. FIG.50 shows a side view of the example of FIG.49 and shows an example of headrest movement and an example of pressure pad movement. FIGS.51 and 52 show views of the example of FIG.49 in an entry orientation. FIGS.53 - 59 show additional views of the example of FIG.49. FIGS.60 and 61 show the example of FIG.49 with the headrest in a first position. FIG.61 depicts a user during treatment in a first orientation. FIGS.62 and 63 show the example of FIG.49 with the headrest in a second position. FIG.63 depicts a user during treatment in a second orientation. FIG.64 shows another example of a therapeutic support device in an entry orientation. FIG.65 shows the example of FIG.16 in a treatment orientation. FIG.66 shows the example of FIG.16 with a headrest location adjustment mechanism in an extended orientation. FIG.67 shows an example of a drive mechanism for a headrest. FIG.69 shows a graphical representation of position versus time for operation of the cerebrospinal fluid pump in an idealized situation. FIG.70 shows a graphical representation of velocity versus time for operation of the cerebrospinal fluid pump in the idealized situation. FIG.71 shows a graphical representation in the subject of airflow over time. FIG.72 shows a graphical representation of operation of the cerebrospinal fluid pump with acceleration and deceleration of movement of the cerebrospinal fluid pump. FIG.73 shows in detail error correction during operation of the cerebrospinal fluid pump with acceleration and deceleration of movement of the cerebrospinal fluid pump. FIG.74 shows a graphical representation of operation of the cerebrospinal fluid pump with acceleration and deceleration of movement of the cerebrospinal fluid pump with a sawtooth waveform for the velocity curve. FIG.75 shows a method for using the CSF pump device 10 to treat the user 12 during a treatment session. DETAILED DESCRIPTION This application may be directed to devices, systems, and methods for improving cerebrospinal fluid dynamics, treating diseases associated with dysfunctional cerebrospinal fluid Z. Grajcar DKT. NO.408439-X dynamics, and improving moto-glymphatic management for brain health and central nervous system health in users with and without diseases. While this disclosure may be embodied in many different forms, there are described in detail herein specific embodiments. This description may be an exemplification of the principles of the disclosure and may be not intended to limit the disclosure to the particular embodiments illustrated or described. For the purposes of this disclosure, like reference numerals in the FIGS. shall refer to like features unless otherwise indicated. Therapeutic support devic set another two-minute time or e, systems, and methods are directed towards optimizing cerebrospinal fluid dynamics in patients and otherwise healthy individuals. In some embodiments, a therapeutic support device may comprise a base, a thigh rest frame supported by the base and a back frame supported by the base. A back support may be attached to the back frame. A headrest may be movable with respect to the back frame about a headrest access. The back support may define a reference plain. They headrest access may be oriented to a front side of the reference plane and the back frame oriented to a second side of the reference plane. DEFINITIONS Fluid dynamics is a subdiscipline of fluid mechanics that describes the flow of fluids. Flow describes movement of fluid produced by a pressure gradient on the fluid. Flux is the rate of flow of per unit area. As used herein, flux will mean the effective flow (subtracting the flow in a first direction from the flow in an opposite, second direction). For example, cerebrospinal fluid flow may be measured using MRI or other techniques. Pump is a device that raises, transfers, delivers, or compresses fluids especially by suction or pressure or both. To pump fluid is to move a fluid with a pump device, otherwise known simply as a pump. FIG.1 shows in standard anatomic position a body 411 of an user 12 with a head 402 turned to the left and FIG.2 shows sectional side view of the head 402 supported by a torso 403. (As used herein, the user may be an individual, patient, subject or other user of the disclosed material.) The user 12 can be a human being that is male (as shown), female, or non-binary. The torso 403 is a main part of the body 411 that contains a chest 404 (also known as a thoracic cavity 404), an abdomen 405 (also known as an abdominal cavity 405), a pelvis 406 (also known as pelvic cavity 406), and a back 407. The chest 404 contains cardiovascular system, including a heart 425. The chest 404 contains respiratory system, including lungs 426 and trachea 427. The back 407 is the rear part, or posterior, of the body 411 of the user 12, especially from the neck Z. Grajcar DKT. NO.408439-X 408 to the end of the spine (see FIG. B5). A diaphragm 428 separates the thoracic cavity 404 from the abdominal cavity 405. Most organs of the body 411 are found in the torso 403, also called a trunk 403. The torso 403 is a central part, or core, of the body 411 of the user 12 from which extend a neck 408, an upper extremity 409, and a lower extremity 410. Limb is another term for extremity. The neck 408 extends superiorly to support and move the head 402 in relation to the torso 403. The head 402 contains intracranially a brain 424; and visual, olfactory, gustatory, and auditory senses. Visual sense is relating to the sense of vision of eyes and associated structures. Olfactory sense is relating to the sense of smell of nose and associated structures. Gustatory sense is relating to the sense of taste of mouth and associated structures. Auditory sense is related to sense of hearing of ears and associated structures. Further, the body 411 of the user 12 has tactile sense, which is relating to the sense of touch. The pair of the upper extremity 409 is parallel to each other and extend distally and inferiorly to the hands 412 with palms facing anteriorly in a standard anatomic position. The upper extremities 409 move the hands 412 in relation to the torso 403. The hands 412 are used for grasping objects. The lower extremities 410 are positioned parallel to each other and extend distally and inferiorly to the torso 403. The pair of the lower extremity 410 extends distally from the torso 403 as a thigh 413 that is moveable with respect to the torso 403 at the hip 414. The thigh 413 extends distally to a leg 415 that is moveable with respect to the thigh 413 at a knee 416, i.e., the thigh 413 is located between the hip 414 and the knee 416. The leg 415 extends distally to a foot 417 that is moveable with respect to the leg 415 at an ankle 418, i.e., the leg 415 is between the knee 416 and the ankle 418. The lower extremities 410 are used for locomotion. A waist 419 of the body 411 is a narrowed part of the torso 403 between hip 414 and chest 404, and the waist 419 is typically taken to be at the level of an umbilicus 420. An upper body 421 includes all body parts superior to the waist 419. A lower body 422 includes all body parts inferior to the waist 419. A midline 423 divides right side and left side of the body 411. Internal describes existing or situated within the limits of something. Skin 430 is an external limiting tissue layer of the body 411 of the user 12. External describes existing at, on, or outside of something. For example, a cerebrospinal fluid system (also known herein as a CSF system) 431 of the user 12 is internal to the body 411 of the user 12; and, except at certain defined areas of egress, cerebrospinal fluid 432 is internal to the CSF system 431 of the user 12. Anterior 433 is situated towards a front of the user 12. Posterior 434 is situated behind or towards a back 407 of the user 12. Rostral direction 435 is directed towards face 436 of the Z. Grajcar DKT. NO.408439-X individual 411. Superior is situated toward the head 402 and further away from the foot 417 than another part of the body 411 that is upright. Caudal direction 437 is directed towards tailbone of the user 12. Inferior is situated below and closer to the foot 417 than another part of the body 411 that is upright. FIG.3 shows the user 12 in supine, which is defined as lying on a back 407 of the user 12 or with the face 436 of the user 12 upward. Supinate is to cause to undergo supination. Supination is the position resulting from supination. FIG.4 shows the user 12 in prone, which is defined as having a front 438 of the body 10 of the user 12 with face 436 downward or lying with the chest 404 and the abdomen 405 of a user 12 facing downward. Pronate is to cause to undergo pronation. Pronation is the position resulting from pronation. FIG.5 shows a side view of a spine 439, also known as a spinal column or a vertebral column, is the axial skeleton of a vertebrate that consists of an articulated series of vertebrae which extend from a neck 408 to a tailbone 440 and protects a spinal cord 441 in the user 12, which shown looking to the right. The articulations include a intervertebral disc 442, which is flexible, disposed between a pair of adjacent vertebrae 443 so that that the spine 439 can achieve positions of flexion and extension and rotation or any combination thereof. The posture of the spine, which is normal, has an S-shaped curve when viewed from the side for cervical spine segment 444, thoracic spine segment 4445, and lumbar spine segment 446 in the user 12 that is standing upright. The cervical spine segment 444 curves slightly inward, sometimes described as a backward C-shape or lordotic curve in a person in normal condition. In the spine 439 that is normal, the cervical lordotic curve is about 30 to about 35 degrees. The thoracic spine segment 445 curves outward, forming a regular C-shape with the opening at the front—or a kyphotic curve—in the person in normal condition. In the spine 439 that is normal, the thoracic kyphotic curve is about 40 degrees. The lumbar spine segment 446 curves inward and, similar to the cervical spine segment 444, has a lordotic or backward C-shape in the person in normal condition. In the spine 439 that is normal, the lumbar lordotic curve is about 45 degrees. When the person is laying supine, in relation to the posture when standing upright, there is a slight straightening of the spine 439 so the cervical spine segment 444 is in flexion; the thoracic spine segment 445 is in extension; and the lumbar spine segment 446 is in flexion. When the person is laying prone, in relation to the posture when standing upright, there is a slight Z. Grajcar DKT. NO.408439-X straightening of the spine 439 so the cervical spine segment 444 is in extension; the thoracic spine segment 445 is in flexion; and the lumbar spine segment 446 is in extension. FIG.6, along with FIG.5, shows in schematic posterior motion of the spine 439 produces flexion of the spine 439, and anterior motion of the spine 439 produces extension of the spine 439. Flex is to bend, especially repeatedly. Bend is to increase or decrease a curve. Flexure is the state of being flexed or bent. For spine 439, flexion is an anterior bending of the torso 403 (see FIG.2), while extension involves a posterior-directed motion (see FIG.2), such as arching of the spine 439. For the extremities, flexion refers to a movement that decreases the angle between two body parts, while extension refers to a movement that increases the angle between two body parts. The vertebral column consists of 7 cervical, 12 thoracic, 5 lumbar, 5 sacral (and normally fused), and 1 coccygeal (and typically fused) segments. Cervical spine segment 444 of the spine 439 is closest to a neck 408 of the user 12. Thoracic spine segment 444 of the spine 439 extends from the cervical spine segment 444 towards the tailbone 440. Lumbar spine segment 446 of the spine 439 extends from the thoracic spine segment 445 towards the tailbone 440. Sacral spine segment 447 of the spine 439 extends from the lumbar spine segment 446 towards the tailbone 440. The coccygeal vertebrae, also known as the coccyx, is commonly referred to as the tailbone 440 and is the end of the spine 439. In each spine segment of the spine 439, the lower numbered vertebrae is rostral, e.g., lumbar 1 is rostral to lumbar 2. The spinal cord is a cord of nervous tissue in the CNS that extends from the brain lengthwise along a back of the person in the spinal canal and gives off pairs of spinal nerves at each segment of the spinal cord. The spinal cord divides into 31 segments: 8 cervical, 12 thoracic, 5 lumbar, 5 sacral, and 1 coccygeal. These segments consist of 31 pairs of spinal nerves with their respective spinal root ganglia. Spinal nerves contain the motor, sensory, and autonomic fibers. These nerves exit through the intervertebral foramen to the right and left of the spinal cord. The spinal nerves L2 to S1 makes up a cauda equina present within the subarachnoid space called a lumbar cistern 449 from about spine L2 to about spine S2. The CSF system 431 is posterior to the vertebrae of the spine 439. In each segment of the spinal nerves, the lower numbered nerve is rostral, e.g., L1 (lumbar 1) is rostral to L2 (lumbar 2). FIG.7 shows a side view of brain 450 and upper portion of the spinal cord 441. Brain 450 is a portion of the Central Nervous System enclosed in a skull 451 of the body 411 and continuous with the spinal cord 441 through a foramen magnum in base of the skull 451. The brain 450 is inside the skull 451, so it is intracranial. The brain 450 is composed of neurons and supporting structures (e.g., glia). The brain 450 integrates sensory information from inside and outside the Z. Grajcar DKT. NO.408439-X body 411 in coordinating motor responses, controlling autonomic function (e.g., heartbeat and respiration), and learning. Neurocognitive has to do with the ability to think and reason, which includes the ability to concentrate, remember things, process information, learn, speak, and understand. Cerebrospinal fluid (also known as CSF), when normal, is a clear, colorless liquid that is secreted from the blood into the lateral ventricles of the brain and serves chiefly to maintain uniform pressure within the brain 450 and spinal cord 441. Cerebrospinal fluid system includes ventricles 452 internal to the brain 450 of the user 12. The ventricles 452 are in fluid communication with a subarachnoid space 453 around the brain 450 and spinal cord 441 in the normal condition. Further details of the CSF are discussed hereinbelow in the context of the Moto-Glymphatic Theory. Meninges are three membranes that surround the brain 450 and the spinal cord 441 of the user 12. The meninges are the dura mater, the arachnoid mater, and the pia mater from external to internal orientation. The dura mater envelops the arachnoid mater. CSF is located in the subarachnoid space 453 between the arachnoid mater and the pia mater, which is a thin layer held tightly to the surface of the brain 450 and spinal cord 441. The dura mater is firmly attached to the rim of the foramen magnum and its fibers blend with the periosteum lining within the skull 451 surrounding the brain 450. In a spinal canal 454, which is located posterior to body of the vertebrae in the spine 439, the anterior attachments support and secure the dura mater anteriorly in the spinal canal, while the posterior surface of the dura mater allows greater mobility. In the spinal canal, the dura mater is not attached to vertebral arches of the spinal column, because of the presence of protective fat tissue in between. The thecal sac or dural sac is the membranous sheath of the dura mater that surrounds the spinal cord and the cauda equina, which are the spinal nerves that extend beyond the spinal cord 441. The lumbar cistern 449 is the subarachnoid space 453 in the lower spine. It is an enlargement of the dural sac that is distal to the conus medullaris, which is the end of the spinal cord 441. The lumbar cistern 449 contains CSF and the nerve roots of the cauda equina, and the lumbar cistern 449 is the usual site of lumbar puncture for diagnostic and therapeutic procedures involving the CSF. From a biomechanical standpoint, when the spine 439 moves, the CSF system 431 moves, although the spinal cord 441 itself within the CSF system 431 may not move much. However, the CSF system 431 can move without the spine 441 moving, for example when the dura mater is moved by pushing on the dura between the vertebral arches during a lumbar procedure, or the Z. Grajcar DKT. NO.408439-X person is tilted, for example head down or head up, while the spine held stationary with respect to the person. MOTO-GLYMPHATIC THEORY Our mortality highlights the value of health and the constraints of our evolutionary past. As we age, life grows more fragile. On an evolutionary scale, we transitioned from a mobile hunter- gatherer existence to a technology-driven, sedentary lifestyle that prizes cognitive skills. This shift clashed with our physical evolution, making us vulnerable to modern diseases. Adapting well-tuned biological systems to the environment takes tens of thousands of years, making it implausible to achieve the same level of adaptation in a matter of decades without external assistance. Eventually cells are damaged, arteries harden, toxins build up, and we end up with heart disease, cancer, lung disease, liver failure, or dementia. Add to this inherited DNA defects and abnormalities and epigenetic DNA abnormalities caused by our lifestyles and a living environment full of harmful toxins and chemicals, and your chances of chronic disease multiply drastically. Even with the miraculous engineering of the human body, we can only clean and clear out so much before the damage becomes unbearable, and we need to take drastic measures beyond our own biology to address them. This is especially true for the brain, the central control center within the complex network of the central nervous system, which consists of the brain and spinal cord. The brain alone contains approximately 100 billion neurons and slightly lesser amount of glial cells as recently validated by isotropic fractionator. Each neuron is making on average 7000 synaptic connections, consuming 8.31 × 10−9J energy for each connection and exchanging information in the rates up to 1000 Hz. In total, our brains consume approximately 0.35kWh energy per day which is 100 times more than an average smartphone. This highly active bioenergetic state generates higher levels of metabolic waste products, such as lactate and glutamate, compared to other organs like muscles. Despite an 18-fold higher specific resting metabolic rate compared to skeletal muscle, the brain lacks the extensive lymphatic vasculature that other organs use to recycle undigested proteins and remove metabolic waste buildup from tissues. The brain consumes about 20% to 25% of the body’s total energy expenditure, despite accounting for only about 2% of the body’s total weight. But how does only 1 / 50th of our body mass require 1 / 5th of our total energy, and dealt with to keep up with the high energy demands of the brain in its tightly constrained space of the bony cranium? To better understand how the brain handles all its metabolic waste, toxins, and cellular byproducts, we must first look at the way the rest of the body deals with waste clearance and fluid balance. Z. Grajcar DKT. NO.408439-X FIGS.8-10 shows in schematic view lymphatic vessels, nodes, and organs in humans. Location of cervical lymph nodes 690. FIG.8 displays a schematic map of lymphatic vessels, nodes, and organs. FIG.9 displays a schematic of lymph flow from interstitial spaces between cells into lymph vessels. FIG.10 displays a schematic pathway of lymph flowing into and out of lymph nodes. Our bodies have a very effective and efficient waste clearance mechanism, the lymphatic system. It is a network of vessels, nodes, and organs that help transport lymph throughout the body, maintains fluid balance, transports dietary fats, and assists the immune system by providing a transportation medium. Lymph is a clear fluid that contains white blood cells and plays a crucial role in the immune system and fluid balance. Unlike the circulatory system, which has a pump (the heart) to move blood, the lymphatic system relies on other mechanisms to facilitate the movement of lymph. The primary mechanisms that move lymph in the lymphatic system are muscle contractions, respiratory movements, one-way valves, and external compression. Skeletal muscle contractions and smooth muscle contractions in the walls of lymphatic vessels play a significant role in moving lymph. When muscles contract during activities such as walking or exercising, they squeeze the lymphatic vessels, propelling lymph through the system. Breathing also aids in lymph movement. As you inhale and exhale, pressure changes occur in the thoracic and abdominal cavities, which helps draw lymph upwards towards the chest 404. Lymphatic vessels have one-way valves like those in veins. These valves prevent the backflow of lymph, ensuring that it moves in one direction. External factors like massage, compression garments, or physical therapy can help stimulate lymphatic flow by gently squeezing the lymphatic vessels. The human body has a network of 500-700 tiny trash bins called lymph nodes scattered throughout, with 300 of them stationed around your head and neck 408. These “trash receptacles” are key players in the lymphatic system, filtering and removing waste products. However, none of the lymph nodes are present within the brain or spinal cord. This absence might be due to their unique environment, encased within the bony skull and spinal column, which creates constraints on fluid movement and waste removal compared to other tissues. As blood circulates throughout the body, fluid leaks out of the blood vessels into the tissues. This fluid bathes and feeds the tissues’ cells and forms the interstitial fluid component of the extracellular fluid volume of the body. The lymph vessels collect interstitial fluid from surrounding tissues, which includes metabolic waste products, toxins, damaged cells (including cancer cells), and bacteria. Subsequently, this fluid flows from interconnected lymph vessels into the associated lymph glands. The lymph glands effectively filter out bacteria and damaged cells. Then the lymph progresses into more Z. Grajcar DKT. NO.408439-X extensive lymphatic vessels, eventually converging into larger vessels that unite at the base of the neck 408, ultimately emptying into the thoracic duct. The thoracic duct then empties the lymph back into the blood circulation. Even though it is a complex system, the energy expenditure associated with moving lymph is minimal and is largely a result of the energy expended during everyday activities that involve muscle contraction and movement. The lymphatic system’s flow rate is intertwined with the body’s overall circulation and movement, and the energy required for lymphatic flow is part of the overall energy expenditure incurred during daily activities. The Maximum Entropy Production Principle (MEPP) highlights nature’s drive for non-equilibrium systems to augment their entropy production, creating processes with the minimum energy expenditure and in the most optimal means possible. Because it lacks lymphatic vasculature, the brain must clear extracellular proteins by an alternative pathway called the Glymphatic System. This system is composed of a network of specialized channels that exist within the brain and are responsible for the clearance of waste products and excess fluid from brain tissue. The term “glymphatic system” was coined as a combination of “glial cells” and “lymphatic system.” This coining is because the system involves the glial cells in the brain, specifically the astrocytes, and its function bears resemblance to the lymphatic system. The glymphatic system, a whole-brain perivascular network which facilitates transfer and clearance of solutes from the cerebral interstitial extracellular space, is now recognized as an essential component of brain waste clearance and has revolutionized our understanding of how the brain removes toxins and waste products. This discovery has had significant implications for research into neurodegenerative diseases like Alzheimer’s disease and has opened new avenues for studying brain health and function. Homeostasis of the brain requires constant maintenance of cellular metabolism, fluid homeostasis, and waste elimination. Cerebral blood flow is highly controlled and continuously supplies oxygen and nutrients to sustain brain function. The blood-brain barrier (BBB), which guards the brain from circulating toxins and pathogens. It also precisely controls the flow of ions and molecules between the brain and the rest of the body. The tight junctions of the endothelial cells limit paracellular influx of ions and solutes across the BBB, thereby regulating water transport. The BBB also contains efflux transporters polarized to the luminal surface (the inner surface of a structure), nutrient transporters (carrier mediated transporters), and transporters for transcytosis. Transcytosis is a process where macromolecules traverse the interior of a cell through vesicles formed by encapsulation within the cell membrane, followed by transport and Z. Grajcar DKT. NO.408439-X ejection through the reverse action. While cellular metabolism and the BBB both play important roles in clearing waste, the main pathway through which the brain clears waste solutes is a dedicated perivascular channel network called the “glymphatic system”. According to the glymphatic hypothesis, subarachnoid CSF enters the brain’s interstitial space from the periarterial space through the AQP4 (aquaporin 4) water channel expressed in the astrocyte end-feet (the specialized extensions of astrocytes, a type of glial cell in the brain, which wrap around blood vessels and nerve cells) and then mixes with the interstitial fluid (ISF) and waste solutes in the brain. The exchange of CSF and ISF carries waste products and toxins like Aβ amyloid, which are subsequently removed from the brain through the perivenous efflux pathway. This distinctive anatomy means homeostasis of the brain relies on the exchange of ISF with CSF, and the removal of waste and toxins is through a two-step process. FIG.68 shows schematic of how brain metabolic waste and toxins, including lactate, tau and β-amyloid (Aβ) are cleared from the brain. In the beginning, CSF flows (via bulk flow) from the subarachnoid space. From the PVS (perivascular spaces), CSF is propelled into the interstitial fluid (ISF) space (facilitated by water channels on astrocyte end feet). Bulk flow-driven CSF exchanges with ISF, ultimately connecting to meningeal lymphatic vessels via perivenous conduits. Integrated within the glymphatic system model are four fundamental functional features. 1. Inflow of subarachnoid CSF into the glymphatic system occurs in the direction of blood flow along the periarterial channels and is driven by pressure (bulk flow) generated by arterial pulsation. 2. Influx of CSF and CSF / ISF exchange are required for perivenous waste clearance, with both processes being dependent on AQP4 water channels. 3. Waste solutes present in the ISF are driven toward perivenous channels. This movement suggests that there is a pressure difference between the periarterial PVS and the perivenous PVS. As a result, this pressure gradient induces a bulk flow, also known as advective flow, within the ISF compartment. 4. A crucial feature of waste transport via the glymphatic system is the dependence on the brain’s activity state. This phenomenon was revealed in a pioneering study showing that perivascular CSF influx and waste clearance increased significantly during periods of slow wave sleep (deep sleep) including anesthesia induced slow-wave sleep and were largely absent during wakefulness. The glymphatic perivascular system, considered the primary pathway for clearing waste from the brain, is still regarded as a model framework, with the underlying physiology incompletely understood. Z. Grajcar DKT. NO.408439-X In addition to the Glymphatic Model of perivascular waste transport, research has yielded opposing findings regarding perivascular solute transport including the underlying driving forces (i.e., advection: transfer of heat or matter by flow of fluid or diffusion), which has given rise to different models of waste clearance. The CSF plays a leading role in protecting the Central Nervous System (CNS) and removing its waste. CSF is a clear, colorless fluid that surrounds the brain and spinal cord, forming a protective cushion for the CNS. Most neuroscientists believe CSF is primarily produced by specialized cells known as ependymal cells located in the choroid plexus within the brain’s ventricles – fluid-filled chambers through which CSF circulates. The choroid plexus is composed of a network of blood vessels and ependymal cells that actively transport specific substances from the blood into the CSF, generating an ultrafiltrate of plasma. This process involves the secretion of ions, water, and other substances from the blood into the ventricles, resulting in CSF formation. However, there is compelling evidence suggesting that CSF production fluctuates throughout the day, with the choroid plexuses being the primary source of CSF production only during periods of rest. CSF acts as a shock absorber, protecting the brain and spinal cord from mechanical injuries. It helps to cushion these delicate structures against sudden movements or impacts. The brain is a delicate organ, and it is buoyant in CSF. This buoyancy reduces the effective weight of the brain by about 95%, preventing it from pressing down on the inner surface on the base of the skull. CSF helps maintain a stable chemical environment around the brain by removing waste products and providing essential nutrients. It acts as a medium for the exchange of materials between the blood and the brain, ensuring that the brain’s extracellular environment remains stable. CSF plays a crucial role in the clearance of metabolic waste products from the brain. Proper CSF circulation is essential for brain health and preventing the accumulation of harmful substances. CSF contains immune cells and antibodies that help protect the CNS from infections. Currently, the strongest experimental support suggests an outflow of CSF at the cribriform plate, where lymphatic vessels transport the fluid and solutes to the deep cervical lymph nodes. The glymphatic system helps remove waste products, including toxic proteins like beta- amyloid and tau, from the brain, playing a crucial role in maintaining brain health and preventing neurological diseases. One of the primary functions of the glymphatic system is to clear away metabolic waste products that accumulate in the brain. Proper functioning of the glymphatic system is essential for overall brain health. Studies have shown that the glymphatic system is more active during sleep. Impaired glymphatic function can lead to increased neuroinflammation. which is a common feature of many neurological diseases, including multiple sclerosis and Parkinson’s disease. Z. Grajcar DKT. NO.408439-X Inflammatory processes can further impair the glymphatic system, creating a cycle that exacerbates neurological conditions. Traumatic brain injury can impair the glymphatic system, leading to the accumulation of harmful substances in the brain. This impairment is thought to be a factor in the development of chronic traumatic encephalopathy (CTE), a degenerative brain disease found in individuals with a history of repetitive brain trauma, such as athletes and military veterans. Improved CSF flux and dynamics may improve the health of people with neurocognitive disorders, subjects who are bedridden, subjects with stroke, subjects with Alzheimer’s disease, and other neurodegenerative diseases such as Parkinson’s, Huntington’s dementia, prion disease cognitive decline, and multiple sclerosis. Improvement may be noted in subjects with brain injury, seizures, tremor, trigeminal neuralgia, and migraines. It may also improve sleep patterns, memory, and symptoms of depression, bipolar disorder, and attention deficit disorder. Neuroinflammation may be reduced. Because the brain and spinal cord in the CSF system are encapsulated by a skull and vertebrae, the fluid within this system (for the most part) cannot be controlled or manipulated as it is elsewhere in the body. Vessels such as arteries and veins, and lymphatics in the rest of the body, are assisted in their transport of fluid (blood, lymph) to tissue throughout the body by the pressure gradient caused by intrinsic forces, including the expansion and contraction of the heart and smooth muscle within the walls of these vessels and extrinsic forces, such as the expansion and contraction of adjacent structures (e.g. muscles, lungs, etc..). In the lower pressure vessels of the venous circulation and lymphatic system, there are also one-way check valves in these vessels that help prevent back flow and pooling of blood or lymph. These vascular structures keep blood or lymph moving in the right direction to their appropriate destination, often against gravity, as seen in the veins of the legs. It is important to note that extrinsic “pumping” in the lymphatic system can create much higher pressure gradients, which results in major effects on lymph flow, causing up to 10-fold more lymph flow compared to intrinsic “pumping”. Unlike the venous and lymphatic circulations in the body, the glymphatic system must abide by the Monro-Kellie doctrine, which states that the total volume of the brain, CSF, and intracranial blood is constant. Therefore, an increase in one volume should decrease one or both of the other volumes. This model proposes that the glymphatic system, which transports CSF and waste products between the brain and body via perivascular channels, is constrained by these intracranial volume dynamics. Considering the tremendous energy consumption of the brain and the perivascular brain waste clearance pathways illustrated in, it seems highly unlikely that current estimates of the daily Z. Grajcar DKT. NO.408439-X production and circulation volume of CSF are accurate. The historically defined volumes of 500 to 700 mL of CSF produced per day and approximately 150 mL of CSF circulating in the system at a given moment must certainly fall short. While our understanding of CSF dynamics is continually evolving, several physical and biomechanical principles and procedures have been scientifically established that affect CSF movement. At rest, CSF is primarily produced in the choroid plexus within the brain’s ventricles and is absorbed into the bloodstream in the arachnoid villi. With movement of the CSF system, CSF is produced in other areas, such as the lumbar cistern that allows in interstitial fluid that becomes CSF in the subarachnoid space. The balance between CSF production and absorption is crucial for maintaining a stable CSF volume and pressure. The movement of CSF is influenced by fluid dynamics principles, such as Bernoulli’s principle, which describes the relationship between fluid pressure and fluid velocity. Changes in pressure gradients and flow rates do impact CSF circulation. The rhythmic heartbeat creates CSF pulsation. During systole (the heart’s contraction phase), CSF in perivascular spaces is displaced by dilatating vasculature, while during diastole (the heart’s relaxation phase), CSF is drawn back into perivascular spaces. Body posture, physical activity, and changes in body position can also influence CSF circulation. For example, an upright posture and physical activity may facilitate CSF movement, potentially more than changes in heart rate alone. The respiratory cycle regulates CSF movement. Respiration creates a pulsation or rhythmic fluctuation in CSF flow. This is due to the cyclical changes in thoracic pressure that occur during breathing. Specifically, during inspiration, the expansion of the chest cavity 404 lowers intrathoracic pressure. This draws more venous blood into the thorax, increasing blood volume and pressure in the thoracic vasculature. The increased pressure is then transmitted to the CSF space, causing a brief rise in CSF pressure with each inhalation. The cyclical fluctuations in CSF pressure due to respiration create a pulsation or rhythmic pumping of CSF within the brain and spinal cord. Studies have consistently found that forced inspiration is associated with an upward CSF movement in the entire spinal canal, causing unidirectional CSF flow in the brain. Brain and spinal cord tissue has a certain degree of compliance, allowing it to expand and contract slightly in response to changes in CSF pressure. This compliance influences CSF dynamics. Ependymal cells lining the ventricles (fluid-filled spaces within the brain) have cilia that help propel CSF through the ventricular system. This ciliary action aids in the circulation of CSF. Z. Grajcar DKT. NO.408439-X The ventricles, subarachnoid space (lining the brain and spinal cord), cranial cavity (housing the brain), central canal (within the spinal cord), and spinal canal (enclosed by vertebrae) all experience different pressure levels. These variations in pressure create pressure gradients that contribute to the movement of CSF within the central nervous system and are essential for maintaining proper circulation. The movement of CSF follows specific pathways through the brain and spine, including the ventricular system, the subarachnoid space, the central canal, and the spinal canal. Obstructions or abnormalities in these pathways can disrupt CSF flow. Various medical conditions, such as hydrocephalus, tumors, and cysts, can disrupt CSF circulation. Understanding the underlying biomechanical changes in these conditions is crucial for diagnosis and treatment. What can be observed in the above categories is that there are only a few ways a person can really alter their CSF flow - heart rate, breathing, posture, and physical activity. Science now clearly shows that forced respiration drives cerebrospinal fluid (CSF) movement (flux) in the brain and spinal canal. This is caused by the fluctuations in the intrathoracic and intrabdominal pressure that occur during the breathing cycle. This phenomenon is now known as respiration-induced CSF flow. When you breathe, changes in pressure within the thoracic and abdominal cavities create a pumping action that helps circulate CSF around the brain and spinal cord. Quiet breathing creates measurable CSF pulsations in the human spine and cerebrum, while forced respiration creates rostral CSF flux (the forward movement of CSF towards the head 402) – rostral flow is volumetrically higher than caudal flow. Our respiration cycle has a direct relationship with cerebrospinal fluid dynamics. As shown in numerous studies, deep abdominal breathing or diaphragmatic breathing has a dramatic effect on cerebral spinal fluid flow and thus the glymphatic system of our brain. Research suggests that meditative and wellness practices, such as yoga and tai chi, which often incorporate focused breathing, may benefit brain health and cognitive function. During deep abdominal breathing, the pressure within your thoracic and abdominal cavities increases, creating a pumping action that helps circulate your CSF. In 2021, a study by Dr. Yildiz revealed a surge in CSF movement during yoga breathing compared to quiet breathing. Interestingly, the most significant changes occurred during deep abdominal breathing. However, a puzzle remains. While this study and others report increased CSF flow during deep breathing, these findings contradict current understanding of how blood flow affects CSF. Peristaltic pumping theory states that surrounding blood vessels must pulsate to propel CSF. But for this model to explain the measured increases in CSF flow, blood vessels would need to pulsate at unrealistic amplitudes, beyond what’s observed in the body. Z. Grajcar DKT. NO.408439-X We hypothesize that, in addition to CSF pulsations driven by cardiovascular and respiratory activity, there are two additional CSF oscillators, that are by far the largest ones – (1) the physical motion of human spine and (2) hydrostatic pressure. Deep breathing that engages your abdomen can boost its impact by incorporating various spinal cord postures. In this way, your spine and brain work like a pump, rhythmically squeezing and releasing, which moves CSF around your nervous system (see FIG.7). When you take a deep cleansing breath, you are augmenting your glymphatic system and increasing waste clearance. Accumulation of metabolites, toxic proteins, and waste in the brain and spinal cord is certainly a component of several neurological disease pathologies. Though the waste and toxins that accumulate may be due to different processes, the overall result may cause similar damage to the proper functioning of the brain and glymphatic system. These accumulations of metabolites, toxins, and waste products in the CSF affect synaptic firing (when a signal travels across a tiny communication bridge between nerve cells) and overall functioning of the brain. Over time, our bodies have evolved and adapted to various environmental threats. However, one of the significant challenges we face today is physical stagnation and the decline of activities that once supported our glymphatic system. As we age, we tend to become less active. We no longer engage in physically demanding tasks like farming or foraging, neglecting the very processes that our bodies rely on for optimal function. Recognizing the need to improve waste removal in the brain and CNS, we researched how our bodies naturally enhance this process through breathing and spinal movements. This research led to the development of a unique, non-invasive device that stimulates CSF flow. Importantly, unlike other methods, this device can increase CSF flow even during light sleep and offers unprecedented control over the rate and frequency of these pulsations. Our device aims to boost the glymphatic system’s natural waste removal process, a process that is most active during sleep or when engaging in specific exercises like yoga, breathing techniques, and stretching. This could potentially provide a novel solution for enhancing glymphatic clearance, addressing a currently unmet need. Through the use of a CSF pump of the present disclosure, the glymphatic system performance is improved and the effects of injuries, infections, toxins, neurodegenerative diseases, and aging on the brain are decreased. According to the Moto-Glymphatic Theory, the cerebrospinal fluid clearance can be increased through increased pressure in the cerebrospinal fluid system. Pressure in the cerebrospinal fluid system is affected by cardiac system activity (heartbeat, etc.), respiratory system activity (respiration, etc.), and movement (of the cerebrospinal fluid system, etc.) The disclosure Z. Grajcar DKT. NO.408439-X describes devices, systems, and methods to increase pressure in the cerebrospinal fluid system through pumps working on the cerebrospinal fluid in the cerebrospinal fluid system of the user. CEREBROSPINAL FLUID PUMPS AND DEVICES HYDROSTATIC PUMPS Hydrostatic pressure is the pressure exerted by a fluid at equilibrium at a given point within the fluid, due to the force of gravity. Hydrostatic pressure increases in proportion to depth measured from the surface because of the increasing weight of fluid exerting downward force from above. Hydrostatic pressure refers to the pressure that any fluid in a confined space exerts. If fluid is in a container, there will be some pressure on the wall of that container. If we picture a column shaped container, we can see that the pressure pushing against its wall is greater at the bottom, than it will be at the top. This is partly related to the force of gravity. Hydrostatic pressure is the pressure that is exerted by a fluid at equilibrium at a given point within the fluid, due to the force of gravity. Hydrostatic pressure increases in proportion to depth measured from a highest point of the fluid because of the increasing weight of fluid exerting downward force from above. FIG.11 shows a side view of a cerebrospinal fluid (CSF) pump 100. As will be developed in this disclosure, it will be understood that CSF pump 100 may be characterized as a CSF pump device 10 or a therapeutic support device 10. FIG.12 shows close up of a portion of the CSF pump device 10 of FIG.11. The user 12 may be shown throughout the disclosure schematically and might not be in proportion so that a CSF system 431 and other details disclosed and discussed may be visualized more easily. A support surface 502 of the CSF pump device 10 may be configured to support the user 12 in a supine position. The support surface 502 may be defined as a reference line 504. The support surface 502 may be contactingly adjacent to the user 12. The support surface 502 may be substantially parallel to a supporting surface 30, such as a floor 30, configured to support the CSF pump device 10 at a height 600. The CSF pump device 10 includes one or more legs 508 to support the support surface 502 above the floor 30. The position of the support surface 502 substantially parallel to the floor 30 may be called a first treatment position (also known herein as FTP). The FTP may be a default position, and the default position may be used for adjusting the CSF pump device 10 to fit the user 12. FTP may be a starting position in a cycle of positions for the CSF pump device 10. The support surface 502 may be a position other than substantially parallel to the support surface 502 in the FTP. FIG.12 shows height 510 of a column of fluid in the cerebrospinal fluid (CSF) system 431 may be measured from the top 514 of the CSF in a cranium 451 to a lowest point 518 of the CSF in the CSF system 431, which might or might not correspond to the end of the CSF system 431 Z. Grajcar DKT. NO.408439-X in cistern lumbar 449. The lowest point 518 may be somewhere in the area of the CSF system 431 in the thoracic spine segment 445, for example. FIG.13 shows a side view of the CSF pump device 10 in FIG.11. FIG.14 shows close up of a portion of the user 12 on the CSF pump device 10 of FIG.3. The support surface 502 may be shown tilted in a head down position of the head 402 of the user 12 at an arbitrary angle 602 with respect to the reference line 502, which may be horizontal. The head down position may be considered a foot up position of the user 12. The head down position may be achieved by shortening the leg of the CSF pump device 10 towards the head 402 of the user 12, by lengthening the leg 508 of the CSF pump device 10 towards the feet 417 of the user 12, or a combination thereof. The shortening of the leg 508 of the CSF pump device 10 or the lengthening of the leg 508 of the CSF pump device 10 may be achieved by a powered linear actuator in the leg or a pump, stepper motor, etc. The head down position may be considered a second treatment position (STP). FIG.14 shows the height 510 of the column of fluid in the CSF system 431 may be different in the head down position than in the position shown in FIG.12. The hydrostatic pressure may be different in the head down position than shown in FIG.12. The brain experiences increased CSF pressure with the head down. FIG.15 shows a side view the example of the CSF pump device 10 in FIG.11. FIG.16 shows a close up of a portion of the user 12 on the CSF pump device 10 of FIG.15. The support surface 502 may be shown tilted in a foot down position of the feet of the user 12 at an arbitrary angle 600 with respect to the reference line 504. The foot down position may be considered a head up position of the user 12. The feet down position may be achieved by shortening the leg 508 towards the feet of the user 12, by lengthening the leg towards the head 402 of the user 12, or a combination thereof. The shortening of the leg 508 or the lengthening of the leg 509 may be achieved by the powered linear actuator in the leg or a pump, stepper motor, etc. FIG.16 shows height 510 of the column of fluid in the CSF system may be different in the head down position than in the FIG.12. The hydrostatic pressure may be different in the head up position than in the FTP. The brain experiences decreased CSF pressure with the head up. In a treatment cycle, the CSF pump device 10 transitions from FTP to STP and back to FTP. The CSF pump device 10 may be substantially parallel to the floor 30 in FTP. The CSF pump device 10 may be head up in relation to the floor 30 in FTP. The CSF pump device 10 may be head down in relation to the floor 30 in FTP. The CSF pump device 10 may be substantially parallel to the floor 30 in STP. The CSF pump device 10 may be head up in relation to the floor 30 in STP. The CSF pump device 10 may be head down in relation to the floor 30 in STP. FIG.17 shows a side view of a portion of the CSF pump device 10.3 positions that may be considered head down or foot down are shown. These positions are sometimes known as Z. Grajcar DKT. NO.408439-X Trendelenburg and reverse Trendelenburg respectively in the medical literature. In any event, the 3 positions correspond to 1) maximum operation range 610 of the CSF pump device 10 for this direction defined by a mechanical obstruction 516, 2) maximum operation range 612 of the CSF pump device 10 for this direction defined by a software restriction, and 3) maximum operation range 614 of the CSF pump device 10 for this direction defined by a user 12. More specifically, the maximum operation range 610 of the CSF pump device 10 for this direction defined by the mechanical obstruction 516 may be the physical limit of the CSF pump device 10 in this direction. However, the operator might not want the CSF pump device 10 to reach the mechanical obstruction 516, because that may damage the CSF pump device 10. Therefore, the maximum operation range 612 of the CSF pump device 10 for this direction defined by the software restriction may be a software limit of the CSF pump device 10 in this direction. The software restriction may be programmed based on the specifications of the CSF pump device 10. In addition, the software restriction may be responsive to the CSF pump device 10 positions. A proximity sensor 514 may detect when the support structure 548 may be in close proximity to the mechanical obstruction 516 in the CSF pump device 10. While the mechanical obstruction 516 may be configured for safety of the user 12, the software restriction may be configured for safety of both user 12 and the CSF pump device 10. Maximum operation range 614 of the CSF pump device 10 for this direction defined by the user 12 may be selected based on user 12 preference, the operator (person operating the CSF pump device 10 device who might not be the user 12) preference, or any other suitable selection criteria. FIG.18 shows a schematic representation of a control system for the CSF pump device 10 shown in FIGS.11 through 17, and any other CSF pump device, therapeutic support device, CSF pump etc. disclosed herein. The control system or variations on the control system may be used for any other CSF pump disclosed. A network 520 connects the various components of the control system. A controller 518 controls configuration and operation of the CSF pump device 10, and the controller 518 may be connected to the network 520. The actuator 522, the stepper motor, etc. controls movement of the CSF pump device 10 back and forth from FTP to STP, and the actuator 522, the stepper motor, etc. may be connected to the network. The controller 518 may be configured to use the actuator 522, the stepper motor, the etc. to control movement of the CSF pump device 10. Power source 524 may be mains, battery, solar, etc. for the network 520 and devices to the network. Any control interface and protocols may be used. MODBUS may be used. MODBUS is a serial communication protocol developed by Modicon published by Modicon® in 1979 for use with its programmable logic controllers (PLCs). In simple terms, it may be a method used for transmitting information over serial lines between electronic devices. MODBUS is an open Z. Grajcar DKT. NO.408439-X protocol. It has become a standard communications protocol in industry, and is now the most commonly available means of connecting industrial electronic devices. MODBUS can operate over different physical layers, such as RS-232, RS-485, or Ethernet. A BUS network a type of network topology in which all devices may be connected to a single communication line, known as the bus. This central line serves as the backbone for data transmission, allowing devices to share information and resources. A BUS HUB is an implementation that allows for interconnection of devices to the BUS. There may be a primary microcontroller unit (MCU) and one or more secondary MCU. The control interface 528 might not be limited to a tablet. Other devices which may connect to the primary MCU via wired or wireless connection may also serve as the control interface 528. There may be a security implementation to prevent connection by unauthorized devices. The proximity sensor 514 monitors the position of the CSF pump device 10 device, and the proximity sensor 514 may be connected to the network. The controller 518 may be configured to use information sensed by the proximity sensor 514 to provide responsive movement of the CSF pump device 10. The controller 518 shuts down the CSF pump device 10 if the maximum range of the CSF pump 100 defined by the CSF restriction may be exceeded. The controller 518 may shut down with no further movement, or the controller may shut down after returning the CSF pump device 10 to substantially parallel to the floor 30 position. The controller 518 takes an error signal generated by data from the proximity sensor 514 to reset the CSF pump 100 by resetting position of the CSF pump device 10. The controller 518 resets the CSF pump device 10 to a known position, which may be FTP, STP, entry position, home position, or any other arbitrary position. A database 526 of FTP, STP, or other useful information for operation of the CSF pump device 10 may be available, and the database 526 may be connected to the network 520. The controller 518 may be configured to interact with the database 526 and use information in the database 526 to operate the CSF pump 100. A control device 528, such as a hand-held device or a device attached to the CSF pump 100, may be configured to control operation of the CSF pump 100, and the control device 528 may be connected to the network 520. The controller 518 may be configured to interact with the control instructions from the control device 528 to control operation of the CSF pump 100. Other components may be envisioned, such as an emergency stop that immediately stops operation of the CSF pump 100. The emergency stop may be connected to the network 520. The emergency stop may be physically connected to the CSF pump 100. The emergency stop may be wirelessly connected to the CSF pump 100. FIG.19 shows a top view of the CSF pump 100 shown in FIGS.11 through 17. The CSF pump 100 has one or more voluntary safety devices. The CSF pump 100 has a head safety device Z. Grajcar DKT. NO.408439-X 530 configured to prevent the head 402 of the user 12 from extending beyond the support surface 502. The CSF pump 100 has a foot safety device 532 configured to prevent the foot 417 of the user 12 from extending beyond the support surface 502. The CSF pump 100 has one or more handhold 534 configured for the user 12 to voluntarily grasp by the hand to help the user 12 remain in position on the CSF device. The CSF pump 100 has one or more leg 508 configured to support the CSF pump 100 above the floor 30 or other support surface 502. The CSF pump 100 may be built for a predetermined size, however the CSF pump 100 may be sized to be usable by a user 12 of undetermined size when the CSF pump 100 may be built. The predetermined size may be responsive to the height, weight, or other biometric feature of the user 12 who will use the CSF pump 100. The CSF pump 100 may be built to account for different center of gravity, such as center of gravity being closer to the feet in women than in men. To review, FIG.20 shows a schematic timeline for a treatment cycle 590, and FIG.21 shows a schematic timeline for a treatment session 592. The CSF pump 100 alternates between the FTP and the STP during the treatment cycle. The alternating movement between the FTP 580 and the STP 582 may be considered oscillatory movement or motion. The alternating movement between the FTP and the STP may be considered cyclical movement or motion occurs at 570. During set up of the CSF pump 100, the maximum operation range of the CSF pump 100 for the FTP 620 defined by the user 12 may be determined. The maximum operation range of the CSF pump 100 for the FTP 620 defined by the user 12 may be no more than the maximum operation range of the CSF pump 100 for the FTP 622 defined by the software restriction. Maximum operation range of the CSF pump 100 for the FTP defined by the software restriction may be less than the maximum operation of the CSF pump 100 defined by the mechanical obstruction 516 which limit 624. During set up of the CSF pump 100, the maximum operation range of the CSF pump 100 for the STP 630 defined by the user 12 may be determined. The maximum operation of the CSF pump 100 for the STP 630 defined by the user 12 may be no more than the maximum operation range of the CSF pump 100 for the STP 632 defined by the software restriction. Maximum operation range of the CSF pump 100 for the STP 632 defined by the software restriction may be less than the maximum operation of the CSF pump 100 defined by the mechanical obstruction 516, which limit 634. The CSF pump 100 alternates between the FTP and the STP for 1 to N number of the treatment cycles during the treatment session. FIGS.22-27 show a side view of the CSF pump 100. FIG.22 shows a side view of the CSF pump 100. The support surface 502 may be configured to support the user 12 in the supine Z. Grajcar DKT. NO.408439-X position. The support surface 502 defines the reference line 536 that may be substantially parallel to the floor 30 configured to support the CSF pump 100. FIG.23 shows a side view of the CSF pump 100 of FIG.22. The support surface 502 may be configured to support the user 12 in the supine position with the head up. A stepper motor, or other suitable motor, may be configured to rotate a rostral portion of the support surface 502 in relation to a caudal portion of the support surface 502 to achieve the head up position at an arbitrary head up angle 600. FIG.24 shows a side view of the CSF pump 100 of FIG.22. The support surface 502 may be configured to support the user 12 in the supine position with the head down. The stepper motor, or other suitable motor, may be configured to rotate a rostral portion of the support surface 502 in relation to the caudal portion of the support surface 502 to achieve the head down position at an arbitrary head down angle 600. FIG.25 shows a side view of the CSF pump 100. The support surface 502 may be configured to support the user 12 in the supine position with the head up and the foot up. The stepper motor, or other suitable motor, may be configured to rotate the rostral portion of the support surface 502 in relation to the caudal portion of the support surface 502 to achieve the head up position to an arbitrary head up angle 600. The stepper motor, or other suitable motor, may be configured to rotate the caudal portion of the support surface 502 in relation to the rostral portion of the support surface 502 to achieve the foot up position at an arbitrary foot up angle 600. FIG.26 shows a side view of the CSF pump 100 of FIG.25. The support surface 502 may be configured to support the user 12 in the supine position with the feet up. The stepper motor, or other suitable motor may be configured to rotate the caudal portion of the support surface 502 in relation to the rostral portion of the support surface 502 to achieve the foot up position at an arbitrary foot up angle 600. The rostral portion of the support surface 502 may be shown substantially parallel to the ground configured to support the CSF pump 100, however other suitable positions of the rostral portion of the support surface 502 may be envisioned. FIG.27 shows a side view of the CSF pump 100 of FIG.25. The support surface 502 may be configured to support the user 12 in the supine position with the head up. The stepper motor, or other suitable motor may be configured to rotate the rostral portion of the support surface 502 in relation to the caudal portion of the support surface 502 to achieve the head up position at an arbitrary head up angle 600. The caudal portion of the support surface 502 may be shown substantially parallel to the ground 30 configured to support the CSF pump 100, however other suitable positions of the caudal portion of the support surface 502 may be envisioned. Any 2 different positions of the CSF pump 100 in FIGS.22-27 may be used as the FTP and the STP during the treatment cycle to affect the CSF dynamics. Z. Grajcar DKT. NO.408439-X FIGS.28-30 shows a side view of the CSF pump was with some embodiments. The support surface 502 may be configured to support the user 12 in the supine position in what may be commonly known as the zero-gravity position. The support surface 502 comprises 3 support surfaces: backrest 18 configured to support the back 407 of the user 12, thigh rest 16 configured to support the thigh 413 of the user 12, and leg rest 24 configured to support the leg 415 of the user 12. The support surface 502 may be configured to support the heart 425 of the user 12 approximately at the level of the knee 416 of the user 12. The support surface 502 may be configured to support the head 402 of the user 12 inclined an arbitrary head up angle from the horizontal reference line. The arbitrary head up angle may be known as a treatment angle. The support surface 502 may be configured to support the arbitrary head up angle at about 16 degrees from the horizontal reference line. The support surface 502 may be configured to support the knee 416 of the user 12 inclined an arbitrary knee up angle 600 from the horizontal reference line. The arbitrary knee up angle may be known as a treatment angle. The support surface 502 may be configured to support the arbitrary knee up angle at about 16 degrees from the horizontal reference line. The support surface 502 may be configured to support the leg of the user 12 inclined downward in arbitrary leg down angle from a reference line defined by the support surface 502 of the thigh rest. The relationship of the backrest, the thigh rest, and the leg rest may define the zero gravity position. The support surface 502 may be configured to support the user 12 in the supine position. The CSF pump 100 may be configured to rotate the support surface 502 such that the arbitrary head up angle 600 may be decreased, while the relative relationship of the backrest 18 and the thigh rest 16 in the zero gravity position may be maintained. The support surface 502 may be configured to support the user 12 in the supine position. The CSF pump 100 may be configured to rotate the support surface 502 such that the arbitrary head up angle 600 may be increased while the relative position of the backrest and the thigh rest in the zero gravity position may be maintained. Any 2 different positions of the CSF pump 100 in FIGS.28-30 may be used as the FTP and the STP during the treatment cycle to affect the CSF dynamics. This type of the CSF pump 100 in which the support surface 502 may be tilted from the FTP to STP might be viewed as a hydrostatic pump, because the primary source of the pressure may be a height of the CSF. Of course, any movement of the user 12 may be likely to affect shape of the CSF system 431 which leads to pressure change due to action of a peristaltic pump, which will now be discussed in further detail. Z. Grajcar DKT. NO.408439-X Recall that increased pressure may be proportionate to increased flow and flux of the CSF in the CSF system, while decreased pressure may be proportionate to decreased flow and flux of the CSF in the CSF system. PERISTALTIC PUMPS FIGS.31-35 show inside view the CSF pump 100 in accordance with some embodiments. FIG.31 shows a side view of the CSF pump 100. In this case, the CSF pump 100 may be characterized as a thoracolumbar pump, lumbar pump, or thoracic pump. The CSF pump 100 may be positioned on top of the support surface 502. The support surface 502 may be substantially parallel to the supporting surface 30 configured to support the CSF pump 100. The CSF pump 100 may be positioned anywhere along the spine 439 of the user 12. The user 12 may be in the supine position, as shown. The CSF pump 100 may be positioned closest to the upper lumbar spine segment of the user 12. The CSF pump 100 assumes a variety of positions, and this position may be the default position. A head cushion (not shown) may be on the support surface 502, and the head cushion may be configured to support the head 402 of the user 12, for comfort of the user 12. More specifically, the CSF pump 100 may be positioned nearest the lumbar 1- lumbar 2 (L1-L2) segment of the back 407 in relation to other portions of the back 407 of the user 12. A cervical spine arrow 538, a thoracic spine arrow 540, and a lumbar spine arrow 542 indicate that each of the cervical spine 444, thoracic spine 445, and lumbar spine 446 may be all extended towards the support surface 502, which may be what happens to the spine 439 of the user 12 supported in the substantially horizontal position shown when supine. FIG.32 shows a close up of a portion of the CSF pump 100 in FIG.31. The spine 439 surrounds the CSF system 431, however for convenience the spinal column might not be shown. Rather, the CSF system 431 may be shown. To review, the spinal column 439 may be essentially the backbone of the user 12. The CSF system 431 may be made up of the meninges that hold the cerebrospinal fluid. The outer layer of the meninges, known as the dura mater, may be closely attached with and moves along with the spinal column. The support surface 502 may be configured to support the user 12. The CSF pump 100 may be shown positioned on top of the support surface 502. Skin and other tissue, such as the spine (not shown), or clothing or bedding, etc. may be between the CSF pump 100 and the CSF system of the user 12. FIG.33 shows a close-up of a portion of the CSF pump 100 in FIG.31. The CSF pump 100 may be in a recess 544 in the support surface 502, as described shortly, and not shown. The user 12 may be on support surface 502 before the CSF pump 100 may be positioned on the support surface 502, as described shortly. Z. Grajcar DKT. NO.408439-X FIG.34 a side view of the example of the CSF pump 100 in FIG.31. The FTP of the CSF pump 100 may be shown. The CSF pump 100 may be moved from the default position to the FTP. The CSF pump 100 may be extended from the default position to the FTP. The CSF pump 100 may be extended or lengthened away from the support surface 502. The default position and the FTP may be the same. In the FTP, the CSF pump 100 may be contactingly adjacent to the posterior area of the user 12. The posterior area of the user 12 may be the upper lumbar spine. There may be material intervening between the user 12 and the CSF pump 100, such as clothes or safety devices. The operator of the CSF pump 100 assists the user 12 in adjusting the CSF pump 100 from the default position to the FTP. The user 12 adjusts the CSF pump 100 from the default position to the FTP by itself, such as through sensory information obtained by the CSF pump 100 and conveyed to the controller that then uses this information to adjust the CSF pump 100 from the default position to the FTP. FIG.35 shows a side view of the example of the CSF pump 100 in FIG.31. The STP of the CSF pump 100 may be shown. The CSF pump 100 may be extended from the FTP to a second treatment position (STP). The CSF pump 100 may be extended or lengthened away from the support surface 502, which may be a span from the FTP to the STP. The operator adjusts the CSF pump 100 from the FTP to apply force to the posterior surface to extend the spinal column until extension of the spinal column just exceeds comfortable but not so far as to cause pain in the user 12. The operator adjusts the CSF pump 100 from the FTP to apply force to the posterior surface to extend the spinal column until extension of the spinal column may be configured to produce pain intensity of 1 or 2 out 10 in the user 12 on a medical standard 0 to 10 numerical rating scale for measuring pain intensity. See Neurology 2013;80(Suppl3):S49–S53, which may be incorporated herein by reference. Score of 0 may be no pain. Score of 10 may be maximum pain. The movement of the CSF pump 100 from the FTP to the STP applies force to the CSF system that increases pressure of the CSF in the CSF system, and this increased pressure may be experienced as a pressure wave rostrally towards the head of the CSF system and caudally towards the thecal sac of the CSF system. As with the rest of the disclosure, the treatment cycle may be configured to move the CSF pump 100 back and forth between the first treatment position and the second treatment position. And the treatment session may be made up of one or more of the treatment cycles. The control system elsewhere described may be used to control the treatment cycles in the treatment session. FIG.36 shows a top view of the CSF pump 100 in accordance with some embodiments. For clarity and convenience, the user 12 might not be shown. The CSF pump 100 may be located in an aperture 546 in the support surface 502. While the CSF pump 100 may be shown as occupying the entire aperture 546, the CSF pump 100 occupies less than the entire aperture 546. Z. Grajcar DKT. NO.408439-X CSF pump may be fastened to one or more walls of the aperture 546 by any suitable fastener, including but not limited to glue that may be safe for use around subjects. The fastener may be screw, weld, welding, etc. FIGS.37-39 shows a side view of the CSF pump 100 of FIG.36. For clarity and convenience, the user 12 is not shown. The user 12 would use the CSF pump 100 in the supine position, so that the CSF pump 100 would apply force to the posterior region of the user 12. The CSF pump 100 may be located in the aperture 546 in the support surface 502. The support surface 502 may be considered a top layer of a support structure 548. The aperture 546 may be in the support structure 548. The aperture 546 may be shown extending less than fully through an entirety of the support structure 548 from the support surface 502 to an opposing surface. The aperture extends through the entirety of the support structure 548, or in other words extends all the way through the support structure 548 from the top surface to a bottom surface. The CSF pump 100 may be adjusted to the FTP height 648 from the support surface 502 in relation to the user 12. The CSF pump 100 may be adjusted to the STP height 650 from the support surface 502 in relation to the user 12. FIG.40 shows a top view of the CSF pump 100 and accordance with some embodiments. For clarity and convenience, the user 12 might not be shown. The CSF pump 100 may be located in the aperture 546 in the support surface 502. The aperture 546 extends through the entirety of the support structure 548, or in other words all the way through the support structure 548 from the top surface configured to support the user 12 to the bottom surface. The CSF pump 100 may be fastened to the opposing surface of the support structure 548. The CSF pump 100 may be shown substantially flush or level with the support surface 502. The CSF pump 100 may be fastened by screws, welds, glue, welding, etc. FIGS.41-43 show a side view of the CSF pump 100 in FIG.40. The CSF pump 100 may extend through a portion of the aperture 546 in the support structure 548. The CSF pump 100 may be fastened to the opposing surface of the support structure 548. The CSF pump 100 may be shown substantially within a recess of the support structure 548 and may be substantially flush or level with the support surface 502. The CSF pump 100 may be within the recess of the support structure 548 and might not be substantially flush or level with the support surface 502, which might not be shown. The CSF pump 100 may be adjusted to the FTP 648 from the support surface 502 in relation to the user 12. The CSF pump 100 may be adjusted to the STP 650 from the support surface 502 in relation to the user 12. FIG.44 shows a bottom view of the CSF pump 100 and accordance with some embodiments. The FIG.44 shows one to N number of the CSF pump 100s, wherein N may be any integer of one or more. Each of the CSF pump 100s may be fastened to the support structure 548. Each of Z. Grajcar DKT. NO.408439-X the CSF pump 100s may be mobile relative to the support structure 548. Each of the CSF pump 100s may be adjustable along one or more rails, such that the CSF pump 100s may be located relative to the user 12 as needed. FIG.45 shows a cross-section in side view an example of the CSF pump 100 of FIG.44 at section line 660. The FIG.45 shows 1 to N number of the CSF pump 100s, wherein N may be any integer of one or more. Each of the CSF pump 100s may be fastened to the support structure 548. Each of the CSF pump 100s may be individually adjusted to the FTP and the STP for the user 12. PUMP DETAILS The CSF pump device 10 may have any suitable pump for extension and flexion of the spinal column may be used. The CSF pump device 10 comprises a motor, actuation mechanism, drive train, or other suitable device. The CSF pump device 10 may be a bag that may be semi- compliant. The CSF pump 100 may be a bag that may be noncompliant. The bag has an expanded state, and an unexpanded state. The bag may be configured to go from the unexpanded state to the expanded state through introduction of an expansion material, which may be a fluid, such as gas or liquid. The expansion material may be small pellets. The control system controls a pump to provide expansion into the expanded state and deflation into the unexpanded state. The bag operates to provide the force pad described throughout this disclosure. MOTOR AND SENSOR CONSOLIDATED DETAILS A variety of motors, motor drivers, proximity sensors, and support structure 548 positioning actuators may be used. Here is exemplary list of the optional motors and sensors that may be used implementing the information in this disclosure. Motor Drivers: Ding’s Motion DS-CLS6-FRS4. Proximity Sensors: Heschen M5 Inductive Proximity Sensor Switch Shield Type LJ5A3-1- Z / AX Detector 1mm 10-30VDC 150mA NPN Normally Closed(NC) 3 Wire. Support surface positioning actuators: Dewert Megamat 20 Linear Actuators. The adjustment mechanisms may include a Megamat single drive actuator available from DewertOkin GMBH, Kirchlengern GER. Thoracolumbar Pump: Ding’s Motion 23C2225K4-400SCSEK4C-LTF-001 Stepper Motor with DS-CLS6-FRS4 Driver. Cervical Pump: Ding’s Motion 24H2085-300-4BL-PG50-EK4C-LTF-1(REV00) with DS- CLS6-FRS4 Driver. The force pad actuation mechanism may include a stepper linear actuator Z. Grajcar DKT. NO.408439-X available from Dings’ Motion USA, Morgan Hill, CA. The headrest actuation mechanism may include a stepper motor, such as a hybrid rotary stepper motor available from Dings’ Motion USA, Morgan Hill, CA. The headrest actuation mechanism may include a gearbox, for example arranged to reduce speed and increase torque. MODBUS may be used. MODBUS is a serial communication protocol developed by Modicon published by Modicon® in 1979 for use with its programmable logic controllers (PLCs). MODBUS can operate over different physical layers, such as RS-232, RS-485, or Ethernet. Proximity Sensors: Heschen MS Inductive Proximity Sensor Switch Shield Type LJ5A3-l- Z / AX Detector Imm 10-30VDC 150mA NPN Normally Closed (NC) 3 Wire. Physiological measurement devices, including fNIRS and wearable sensors, may be used. The various sensors used to gather information from the user are physiologic sensors configured to measure a physiologic parameter. An apparatus for measuring intracranial dynamics comprises the at least one sensing device (100): an electroencephalographic electrode arrangement, which senses direct-current electroencephalographic signals from the brain, an optic measurement arrangement, which directs optic radiation toward the brain through the cranium, and receives the optic radiation reflected and / or scattered therefrom, and / or a capacitive sensor arrangement, which senses electric potential signals of the head. The apparatus additionally comprises a data processing arrangement, which receives electric signals from the at least one sensing device, and determine data on at least one of the following dynamics: glymphatic activity, water within the cranium, brain tissue movements, water and / or electrolyte movements and intracranial pressure based on said electric signals from the at least one sensing device. The data processing arrangement then outputs at least one piece of the data on the dynamics through a user interface. WO2022180306A3, publication date 01 September 2022, MYLLYA, Teemu and KIVINIEMI, Vesa is incorporated by reference. A method for measuring intracranial dynamics, by performing an optoelectronic measurement of the intracranial neuronal and fluids dynamics, brain tissue pulsation and glymphatic activity through the cranium by an optoelectronic measurement arrangement. Applying, by the data processing unit, at least one of the following analyses to electrical signals received from the optoelectronic measurement arrangement and carrying information on said dynamics. At least one of the pulses of the of the dynamics is decomposed for processing with a relation between the characteristic pulses. A moment of statistical analysis of the pulses of said dynamics is determined. A brain fluid, particularly water-hemodynamic, coupling is determined from the pulses of said dynamics based on a definition Z. Grajcar DKT. NO.408439-X that a sum of volumes of the brain tissue, cerebrospinal fluid (CSF) and intracranial blood is constant. A ratio between a power spectral density of a fraction of a whole measured frequency band and a power spectral density of the whole measured frequency band is determined. Entropy relating to the electrical signals is determined. AG-index based on said analysis of the electrical signals and a reference, which is based on an analysis of a control group with known and / or estimated intracranial dynamics, is determined, the G-index representing a relative dynamics of the brain. WO2024061487Al, publication date 28 March 2024, MYLLYA, Teemu; FERINANDO, Hany; and KIVINIEMI, Vesa. An example of a cardiac activity monitor is Complete Wireless Upper Arm Blood Pressure Monitor and EKG, or similar, is used to record cardiac activity, but other devices may be used of course. Complete Wireless Upper Arm Blood Pressure Monitor and EKG is a product of Omron. An example of a respiration activity monitor is Pulse XS pro is a pulse oximeter that is a product of Oxiline, but other devices may be used of course. Another example of a respiration activity monitor is Capnostream portable respiratory monitor provides monitoring of CO2, SpO2, pulse rate, and respiration rate and is a product of Nellcor. Trackit T4A ambulatory EEG, or similar, records brain activity. Trackit T4A ambulatory EEG is a product of Nihon Kohden Corporation. A Garmin smartwatch vivoactive (Garmin Ltd., Olathe, KS), such as model number 010- 02862-10, may be used to monitor heart rate (HR) via wrist-worn LED PPG, from which HRV can be derived. The device also includes a tri-axial accelerometer for movement tracking, enabling the estimation of sleep stages and RHR during sleep. Data will be collected and analyzed using LabfrontTMHealth Data Analytics, an all-in-one solution for research-grade physiological data management. Daily RHR, RR, and HRV (root-mean-square of successive differences between normal heartbeats, RMSSD) will be extracted via Garmin’s algorithms and analyzed through LabfrontTM Health data analytics. Resting HR and HRV will be assessed during sleep to capture baseline autonomic function. Changes in these metrics will be quantified as the slope of the linear regression line fitted to the daily values over the study period. Sleep metrics, including “Total Sleep Duration,” “Sleep Efficiency,” and “Sleep Score,” will be obtained from Garmin and processed through LabfrontTMHealth data analytics. These measures will be analyzed similarly to the daily HRV, RHR, and RR metrics to assess physiological changes over time. CSF PUMP WITH CERVICAL EXTENSION AND FLEXION Z. Grajcar DKT. NO.408439-X There may be an interesting observation regarding the movement from the FTP to the STP of the CSF pump 100 and movement back to the FTP. When the CSF pump 100 moves from the FTP to the STP, the spine extends or goes into extension. Analogously, the movement from the STP to the FTP of the CSF pump 100 flexes the spine or causes the spine to go into flexion. During normal breathing, the user 12 extends the spine during inspiration. During normal breathing, the user 12 flexes the spine during exhalation. Without any thoughts or intent to extend or flex the spine, the biomechanics of the body of the user 12 result in this movement during inhalation or exhalation. In other words, movement of the CSF pump 100 from the FTP to the STP corresponds to the inhalation phase of breathing in the user 12 in a normal cycle in which the user 12 may be not trying to control the pattern of breathing. In addition, movement of the CSF pump 100 from the STP to the FTP corresponds to the exhalation phase of breathing in the user 12 in a normal breathing cycle in which the user 12 may be not trying to control the pattern of breathing. FIGS.46-48 show a side view an example of the CSF pump 100 in accordance with some embodiments. The user 12 may be supported on the support surface 502 in the supine position. The support surface 502 defines the reference line. The CSF pump 100 may be located adjacent to the cervical spine 444. While the CSF pump 100 located adjacent to the cervical spine 444 could be of the type already presented, the CSF pump 100 adjacent to the cervical spine 444 shown may be a hinge type. The user 12 may be shown in a neutral position without the head cushion, which may be optional, and this position might be known as the default position for the CSF pump 100 adjacent to the cervical spine. There may be the mechanical obstruction 516 configured for maximum operation range of the CSF pump 100 for the direction of extension. There may be the proximity sensor 514 configured for maximum operation range of the CSF pump 100 defined by the software restriction. The user 12 may be supported on the support surface 502 in the supine position. The support surface 502 could be called a headrest 22. The CSF pump 100 adjacent to the cervical spine 444 may be angled an arbitrary angle 600 in a first direction in relation to the reference line defined by the support surface 502. In other words, rotation of the support surface 502 in the first direction may be configured to flex the neck 408 of the user 12. The proximity sensor 514 may be configured for maximum operation range of the CSF pump 100 defined by the software restriction. This configuration may be defined as the FTP. The user 12 may be supported on the support surface 502 in the supine position. The CSF pump 100 adjacent to the cervical spine 444 may be angled in arbitrary angle 600 in a second direction in relation to the reference line defined by the support surface 502. In other words, rotation of the support surface 502 in the second direction may be configured to extend the neck 408 of the user 12. The proximity sensor 514 may be configured for maximum operation range Z. Grajcar DKT. NO.408439-X of the CSF pump 100 defined by the software restriction. This configuration may be defined as the STP. There may be the mechanical obstruction 516 configured for maximum operation range of the CSF pump 100 for the direction of extension. For the CSF pump 100 shown in FIGS.46-48, the proximity sensor 514 may be configured to provide a safety factor to prevent damage to the CSF pump 100. The CSF pump 100 may alternate between the FTP and the STP through a stepper motor. The stepper motor takes a defined number of steps to move the support surface 502 from the FTP to the STP, and the defined number of steps to move the support surface 502 from the STP to the FTP. At each STP, the proximity sensor 514 provides the controller 518 with information regarding the position of the support surface 502 in relation to the mechanical obstruction 516 configured to define the maximum operation range of the CSF pump 100 in the direction towards the STP. If the proximity sensor 514 provides the controller 518 with information that the support surface 502 may be too close to the mechanical obstruction 516, then the controller 518 may be programmed to act upon this too close information. The controller 518 response to the too close information may be configured to immediately stop the CSF pump 100. The controller 518 response to the too close information may be configured to stop the CSF pump 100 after completing one more transition from STP to FTP, which may be more comfortable for the user 12. The controller 518 response to the too close information may be configured to introduce an offset configured to compensate for the stepper motor bringing the support surface 502 too close to the mechanical obstruction 516 and the treatment session continues. The controller 518 may be configured to decrease or eliminate the offset when the information from the proximity sensor 514 indicates the support surface 502 may be not close enough to the mechanical obstruction 516. The controller 518 may be configured to introduce the offset when the maximum operation range of the CSF pump 100 defined by the user 12 may be less than the maximum operation range of the CSF pump 100 defined by the software restriction. A sentencing direction 517 of the proximity sensor 514 is shown. We have now shown the CSF pumps 100 configured to produce the FTP and the STP for the cervical spine 444 and the lower spine, such as the thoracic spine 445 and the lumbar spine 446 the combined thoracic spine and lumbar spine may be referred to as the thoracolumbar spine. And that creates a follow-up to the interesting observation regarding the movement from the FTP to the STP of the CSF pump 100 and back to the FTP for the CSF pump 100 adjacent to the torso 403, and in particular the lumbar spine 446. When the CSF pump 100 adjacent to the cervical spine 444 moves from the FTP to the STP, the cervical spine 444 extends or goes into extension. Analogously, the movement from the FTP to the STP of the CSF pump 100 adjacent to the cervical spine 444 flexes the spine or causes the spine to go into flexion. As previously stated, Z. Grajcar DKT. NO.408439-X during normal breathing, the user 12 extends the spine during inhalation, and the user 12 flexes the spine during exhalation. Without any thoughts or intent to extend or flex the spine, the biomechanics of the body 411 of the user 12 result in this movement during inhalation or exhalation. In other words, movement of the CSF pump 100 from the FTP to the STP corresponds to the inhalation phase of breathing in the user 12 in a normal cycle in which the user 12 might not be trying to control the pattern of breathing. In addition, movement of the CSF pump 100 from the STP to the FTP corresponds to the exhalation phase of breathing in the user 12 in a normal breathing cycle in which the user 12 might not be trying to control the pattern of breathing. Furthermore, while each of the CSF pump 100s used individually might support or reinforce the relationship between movement from the FTP to the STP of the CSF pump 100 in relation to breathing and back again, using the CSF pump 100 on the torso 403, and particularly on the lumbar spine 446, in conjunction with the CSF pump 100 on the cervical spine 444 will not only support or reinforce the relationship between the movements and breathing of the user 12, but the movements may gait the breathing of the user 12 to be in synchrony with inhalation and exhalation with movements of the CSF pump 100s from the FTP to the STP and back again, respectively. CHAIR, TILT TABLE, UPPER BODY TILT TABLE, ZERO-GRAVITY CONFIGURATIONS FIG.49 shows in a perspective view another embodiment of the CSF pump device 10. This position of the CSF pump device 10 may be characterized as an entry position for the user 12 to enter into the CSF pump device 10. The CSF pump device 10 may comprise a base 15 to support the CSF pump device 10 on the supporting surface 30. The base 15 may support a headrest 22, a backrest 18, a thigh rest 16, and a leg rest 24 or any combination of the same. The headrest 22 may be configured to support the head 402 of the user 12 contactingly adjacent to a head support surface 140 of the headrest 22. The backrest 18 may be configured to support the back 407 and buttocks of the user 12 contactingly adjacent to a back support surface 142 of the backrest 18. The thigh rest 16 may be configured to support the buttocks and thigh 413 of the user 12 contactingly adjacent to a thigh support surface 144 of the thigh rest 16. The leg rest 24 may be configured to support the leg 415 of the user 12 contactingly adjacent to a leg support surface 146 of the leg rest 24. The user 12 may be in the supine position on the head support surface 140, the backrest surface 142, the thigh support surface 144, and the leg support surface 146. The CSF pump device 10 may have arm rests configured to support arms of the user 12 contactingly adjacent to an arm support surface 148 of the arm rest. Of note, the backrest 18 may be characterized as the backrest. However, it will be recognized that in the configuration being shown there may be the backrest 18 that corresponds to an upper Z. Grajcar DKT. NO.408439-X portion or 1st portion of the overall backrest and a backrest 20 that corresponds to a lower portion or 2nd portion of the overall backrest. And there may be 3rd portion of the overall backrest that may correspond to the thoracolumbar force pad 28. FIG.21 shows a side view of the LRAM 120 of the CSF device of FIG.20. The LRAM 120 may couple the leg rest 24 to the thigh rest 16. The LRAM 120 may be configured to move the leg rest 24 with respect to the thigh rest 16. The LRAM 120 may include a motor configured to move the leg rest 24 with respect to the thigh rest 16. The LRAM 120 may be configured to rotate an angle of the leg rest 24 with respect to the thigh rest 16. The LRAM 120 may include a motor configured to rotate the angle of the leg rest 24 with respect to the thigh rest 16. The LRAM 120 may include a connection member configured to couple the thigh rest 16 at a first end of the connection member to the leg rest 24 at a second end of the connection member. The first end of the connection member may be configured to rotate with respect to the thigh rest 16. The second end of the connection member may be configured to rotate with respect to the leg rest 24. The second end of the connection member may be captured in a track coupled to the leg rest 24. The leg adjustment mechanism may include a motor configured to lengthen and shorten the connection member. The connection member may be shortened and the second end of the connection member may slide within the track and may interact with a proximal end of the track to rotate the leg rest 24 with respect to the thigh rest 16. The connection member may be shortened and the angle of rotation from the thigh support surface 144 to the leg support surface 146 may be increased. FIG.22 shows a side view of the LRAM 120 of the CSF device of FIG.20. The connection member may be shown lengthened and the second end of the connection member has slid within the track to interact with a distal end of the track to rotate the leg rest 24 with respect to the thigh rest 16. The connection member may be lengthened and the angle of rotation from the thigh support surface 144 to the leg support surface 146 may be decreased. Shown in FIG.50, the support surface 144 of the thigh rest 16 and the support surface 146 of the leg rest 24 may lie substantially in one plane, that may be the support surface 144 of the thigh rest 16 and the support surface 146 of the leg rest 24 may be coplanar. FIG.23 shows a bottom view of the LRAM 120 of the CSF device of FIG.20. The connection member motor may be configured to lengthen and shorten the connection member. A shaft extends from a body of the connection member when the connection member lengthens. A shaft retracts into the body of the connection member when the connection member shortens. The track that may be configured to capture the second end of the connection member may include one or more tracks. The LRAM 120 may include one or more rotation support structure Z. Grajcar DKT. NO.408439-X 548 configured to couple the leg rest 24 to the thigh rest 16. The one or more rotation support structure 548s may be configured to rotate the leg rest 24 with respect to the thigh rest 16. FIGS.24 show side views of the BRAM 50 of the CSF device in FIG.20. The BRAM 50 may couple the backrest to the thigh rest 16. The BRAM 50 may be configured to move the backrest with respect to the thigh rest 16. The BRAM 50 may include a motor configured to move the backrest with respect to the thigh rest 16. The BRAM 50 may be configured to rotate the backrest with respect to the thigh rest 16. The BRAM 50 may include a motor configured to rotate the backrest with respect to the thigh rest 16. The backrest may be coupled to the thigh rest 16 through a backrest thigh rest hinge. The BRAM 50 may be coupled to the backrest and the thigh rest 16, and the BRAM 50 may be configured to move the backrest with respect to the thigh rest 16. A connection member may couple the backrest to the thigh rest 16. The BRAM 50 may be configured to change an angle between the thigh rest 16 and the backrest through lengthening and shortening of the connection member. Shown in FIG.52, the support surface 144 of the thigh rest 16 and the support surface 142 of the backrest 18 may lie substantially in one plane, that may be the support surface 144 of the thigh rest 16 and the support surface 142 of the backrest 18 may be coplanar. Shown in FIG.25, the support surface 144 of the thigh rest 16 may be rotated with respect to the support surface 142 of the backrest 18 through lengthening of the connection member. FIGS.26-28 shows side views of the headrest 22 and a portion of the backrest of the CSF pump device 10 of FIG.20. The headrest 22 may be coupled to the backrest. The headrest 22 may be coupled to the backrest through a crank arm with a first end of the crank arm may be connected anterior to the head support surface 140 and a second end of the crank arm may be connected posterior to the back support surface 142. The crank arm may be curvilinear. A HRLAM 34 may be coupled to the headrest 22 and the backrest, and the HRLAM 34 may be configured to move the headrest 22 with respect to the thigh rest 16. The HRLAM 34 may be configured to move a headrest rotation axis 96 of the headrest 22 with respect to the thigh rest 16. The headrest rotation axis 96 may be anterior to the head support surface 140. The headrest rotation axis 96 may be configured to be just below the chin of the user 12. The headrest rotation axis 96 may be configured to be through the neck 408 of the user 12. FIGS.26 and 26A show the headrest 22 in the FTP 31. The headrest 22 may be rotated anterior to the reference line defined by the backrest. An anterior angle of rotation may be about 60°, or any other suitable angle, with respect to the reference line defined by the backrest. The headrest 22 may be configured to support the head 402 of the user 12 and flex the neck 408 of Z. Grajcar DKT. NO.408439-X the user 12 when the headrest 22 may be rotated anterior to the reference line defined by the backrest. See FIG. XX for further details of the discussion of the 1) maximum operation range of the CSF pump 100 for this direction defined by a mechanical obstruction 516, 2) maximum operation range of the CSF pump 100 for this direction defined by a software restriction, and 3) maximum operation range of the CSF pump 100 for this direction defined by a user 12. The mechanical obstruction 516 may be shown without being hidden by the crank arm. Rotation of the motor in the posterior direction may rotate the headrest 22 from the FTP 31 towards the STP 33. The motor may be a stepper motor that may be configured to rotate a predetermined number of steps from the FTP 31 towards the STP 33. FIGS.27 and 27A show the headrest 22 in the STP 33. The headrest 22 may be rotated posterior to the reference line defined by the backrest. There may be a posterior angle of rotation of about 45°, or any other suitable angle, with respect to the reference line defined by the backrest. The headrest 22 may be configured to support the head 402 of the user 12 and extend the neck 408 of the user 12 when the headrest 22 may be rotated posterior to the reference line defined by the backrest. The mechanical obstruction 516 may be shown in hidden line behind the crank arm coupled to the motor. Rotation of the motor in the anterior direction rotates the headrest 22 from the STP 33 towards the FTP 31. The motor may be a stepper motor that may be configured to rotate a predetermined number of steps from the STP 33 towards the FTP 31. FIG.28 shows the headrest 22 positioned between the FTP 31 and the STP 33. The headrest 22 positioned between the FTP 31 and the STP 33 may be a neutral position. The headrest 22 may be positioned in the neutral position when the CSF pump device 10 may be in the entry position. FIGS.29-31 show side views of the arm rest 26 and the backrest of the CSF device of FIG. 20. The arm rest 26 may be coupled to the backrest. The arm rest 26 may be coupled to the backrest through a connecting connection member. The arm rest 26 may be moveable and pivotable about a central axis of the connecting connection member. The arm rest may be fixed with respect to the backrest. FIG.29 shows the arm rest 26 in the entry position, which may be optional. The angle between the reference line may be defined by the support surface of the backrest and the support surface of the arm rest 26may be about 110 degrees, or any other suitable angle. FIG.30 shows the arm rest 26 in the FTP, which may be optional. The angle between the reference line may be defined by the support surface of the backrest and the support surface of the arm rest 26 may be about 140 degrees, or any other suitable angle. The central axis may be more rostral in the FTP than in the entry position. Z. Grajcar DKT. NO.408439-X FIG.31 shows the arm rest 26 in the STP, which may be optional. Optionally the angle between the reference line defined by the support surface of the backrest and the support surface of the arm rest 26 may be about 160 degrees. The central axis may be more rostral in the STP than in the FTP. The backrest may comprise a lower backrest portion, an upper backrest portion, and a thoracolumbar force pad 28 between the lower backrest portion and the upper backrest portion. The headrest 22 may be coupled to the upper backrest portion. The thigh rest 16 may be coupled to the lower backrest portion. The backrest adjustment portion may be configured to move the headrest 22, the upper backrest portion, the thoracolumbar force pad 28, and the lower backrest portion, or any combination of the headrest 22, the upper backrest portion, the thoracolumbar force pad 28, and the lower backrest portion with respect to the thigh rest 16. The thoracolumbar force pad 28 may be coupled to the backrest. A force pad location adjustment mechanism may be configured to move the thoracolumbar force pad 28 with respect to the headrest 22. The force pad location adjustment mechanism may provide fine control to move the thoracolumbar force pad 28 with respect to the headrest 22. A coarse control to move the thoracolumbar force pad 28 with respect to the headrest 22 may be applied through the BRAM 50. The BRAM 50 may move the thoracolumbar force pad 28 one unit of distance rostral to the lower backrest portion, while the BRAM 50 may move the upper backrest portion a different unit of distance rostral to the lower back portion. The BRAM 50 may move the thoracolumbar force pad 28 one unit of distance rostral to the lower backrest portion, while the BRAM 50 may move the upper backrest portion 2 units of distance rostral to the lower back portion. The ratio of movement of the thoracolumbar force pad 28 relative to the upper backrest portion may be implemented through software control by the controller 518. A TRAM 38 may be coupled to the base 15. The TRAM 38 may be configured to move the thigh rest 16 with respect to the base. The TRAM 38 may be configured to pivot the thigh rest about a thigh rest base hinge with respect to the base 15. The TRAM 38 may be configured to move the leg rest 24, the thigh rest, the backrest, the thoracolumbar force pad 28, and the headrest 22 collectively with respect to the base 15. The TRAM 38 may move the arm rests 26 collectively with the thigh rest 16 with respect to the base 15. A TRAM 38 may be coupled to the base 15. The TRAM 38 may be configured to move the thigh rest 16 (or more generally the leg rest 24, the thigh rest 16, the backrest, and the headrest 22) towards or away from the base 15. The TRAM 38 may be configured to raise or lower the thigh rest 16 with respect to the supporting surface 30. The TRAM 38 more generally characterized as support surface adjustment mechanism, Z. Grajcar DKT. NO.408439-X A force pad actuation mechanism may be configured to move the thoracolumbar force pad 28 into the FTP 41 and the STP 43. The force pad actuation mechanism may be configured to move the thoracolumbar force pad 28 between the FTP 41 and the STP 43 during each treatment cycle during the treatment session. The force pad actuation mechanism may be configured to move the thoracolumbar force pad 28 substantially orthogonal to the backrest. The force pad actuation mechanism may be configured to move the thoracolumbar force pad 28 in a substantially non- orthogonal to the backrest direction. The force pad actuation mechanism may be configured to move the thoracolumbar force pad 28 from an aperture 546 in the thoracolumbar force pad 28 towards the user 12 and into contact with the user 12. The force pad actuation mechanism may be configured to move the thoracolumbar force pad 28 away from the user 12 into the aperture 546 in a recess out of contact with the user 12. The thoracolumbar force pad 28 may be substantially the same width as the upper backrest and the lower backrest. The thoracolumbar force pad 28 might not move during FTP 41 and STP 43. The thoracolumbar force pad 28 might not move during FTP 41 and STP 43 to account for the health issues of the user 12, such as prior low back surgery, degenerative joint disease, etc. A headrest actuation mechanism may be configured to move the headrest 22 with respect to the backrest into the FTP 31 and the STP 33. When the headrest 22 may be in a neutral position the head support surface 140 may be coplanar with the back support surface 142, and movement of the headrest 22 to the FTP 31may correspond to anterior rotation of the headrest 22 with respect to the backrest and movement of the headrest 22 to the STP 33 may correspond to posterior rotation of the headrest 22 with respect to the backrest. The headrest actuation mechanism may be configured to move the headrest 22 about the headrest rotation axis 96 between the FTP 31 and the STP 33 during each treatment cycle during the treatment session. In summary: Adjustment mechanism summary of options: 1. Leg rest adjustment mechanism (LRAM) 120 may be arranged to move the leg rest 24 with respect to the thigh rest 16. 2. Backrest adjustment mechanism (BRAM) 50 may be arranged to move the backrest with respect to the thigh rest 16. The BRAM 50 may be arranged to change an angle between the thigh rest 16 and the backrest. 3. Headrest location adjustment mechanism (HRLAM) 34 may be attached to the first portion of the backrest and to a second portion of the backrest. The movement may be along a linear axis. The HRLAM 34 may be arranged to move the headrest 22 with respect to the thigh Z. Grajcar DKT. NO.408439-X rest 16. The headrest location adjustment may be arranged to move the axis of rotation of the HRLAM 34. 4. Thigh rest adjustment mechanism (TRAM) 38, or more generally support surface adjustment mechanism, may be arranged to move the thigh rest 16 or the support surface with respect to the base 15. 5. Thoracolumbar force pad location adjustment mechanism (TFPLAM) 78 may be arranged to move the thoracolumbar force pad 28 with respect to the headrest 22. The force pad location adjustment may be arranged to move the third portion of the backrest with respect to the second portion of the backrest. The force pad location adjustment mechanism may be arranged to move the third portion of the backrest with respect to the first portion of the backrest. The movement may be along a linear axis. 6. Support surface height adjustment mechanism (SSHAM) 150 may be arranged to change height of the supporting surface 30. Alternatively, the options may be described as follows: A HRLAM 34 may be configured to move the headrest 22 with respect to the backrest. The HRLAM 34 may be configured to move a headrest rotation axis of the headrest 22. A BRAM 50 may be configured to move the backrest with respect to the thigh rest 16. The BRAM 50 may be configured to change an angle between the 16 and the backrest. The BRAM 50 may move the headrest 22, the thoracolumbar force pad 28, the upper backrest, or the lower backrest or a combination thereof with respect to the thigh rest 16. A TRAM 38 may be configured to move the thigh rest 16 with respect to the base 15. The TRAM 38 may be configured to pivot the thigh rest 16 about the hinge with respect to the base 15. The TRAM 38 may be configured to move the thigh rest 16, the backrest, the thoracolumbar force pad 28, and the headrest 22 collectively with respect to the base 15. The TRAM 38 also may move the leg rest 24 and arm rests 26 collectively with the thigh rest 16 with respect to the base 15. A LRAM 120 may be configured to move the leg rest 24 with respect to the thigh rest 16. A TFPLAM 78 configured to move the thoracolumbar force pad 28 with respect to the headrest 22. A thoracolumbar force pad actuation mechanism (TFPAM) 64 configured to move the thoracolumbar force pad 28 between the FTP 41 and the STP 43. A headrest actuation mechanism configured to move the headrest 22 with respect to the backrest. The headrest actuation mechanism may be configured to move the headrest 22 about the headrest rotation axis 96. Z. Grajcar DKT. NO.408439-X The purpose of the actuation mechanisms may be oscillatory movement of the CSF pump 100 between the FTP and the STP during the treatment cycles of the treatment session for the individual. The motors used for the actuation mechanisms may be configured for a heavier duty cycle relative to the motors used for the adjustment mechanisms. The therapeutic support device 10 may be used for the user 12 of indeterminate size. The purpose of the adjustment mechanisms may be to position the CSF pump device 10 in the treatment positions, FTP and STP, that fit the user 12 for the treatment cycles of the treatment session. Of course, the adjustment mechanisms might be used for actuation mechanisms if the motors are configured for a heavy-duty cycle. Of course, the actuation mechanisms may be used for adjustment mechanisms. The HRLAM 34, the BRAM 50, the TRAM 38, the LRAM 120, and the TFPLAM 78 may comprise any suitable type of mechanism, such as an actuator, powered linear actuator, motor, drive system, etc. The HRLAM 34, the BRAM 50, the TRAM 38, the LRAM 120, and the TFPLAM 78 may comprise a Megamat single drive actuator available from DewertOkin GMBH, Kirchlengern GER. The therapeutic support device 10 may comprise one or more of a TFPAM 64. The TFPAM 64 may comprise any suitable mechanism configured to move the thoracolumbar force pad 28 as described herein. The TFPAM 64 may comprise a linear actuator. The TFPAM 64 may comprise a rotational motor configured to turn a screw shaft and a carriage that moves along the length of the screw shaft. The TFPAM 64 may comprise a stepper linear actuator available from Dings’ Motion USA, Morgan Hill, CA. For simplicity of the preceding discussion in this section has shown a first portion, a second portion, and a third portion of the backrest. The first portion of the backrest 18 corresponds to what can be characterized as an upper backrest or upper back support. The second portion of the backrest 20 corresponds to what can be characterized as a lower backrest or lower back support. The third portion of the backrest corresponds to the thoracolumbar force pad 28. The three portions taken together may form the back support surface number 142. The back support surface 142 is configured to support the back 407 of the user 12. The back support surface 142 may be on the first side of the device 10. The second side of the device 10 may be on the opposing side of the device 10. It is contemplated that the back support surface 142 may be one component without the thoracolumbar force pad 28. It is contemplated that the headrest location adjustment mechanism may be used with the one component version of the back support surface 142. The one-piece version of the back support surface is disclosed elsewhere in the present application. Z. Grajcar DKT. NO.408439-X Therapeutic Support Device Here is another example of the therapeutic support device 10, also characterized as the CSF pump device 10. The FIGS.49-67 show various examples of the therapeutic support device 10 and related methods for using the therapeutic support device 10. The therapeutic support device 10 may be used for increasing cerebrospinal fluid (CSF) flux or flow in a user 12 of indeterminate size. FIG.49 shows an embodiment of the therapeutic support device 10. The therapeutic support device 10 may comprise components, such a frame 14, a thigh rest 16, a back support 18, a headrest 22 and a thoracolumbar force pad 28, alone or in any combination thereof. The therapeutic support device 10 may further comprise a leg rest 24, an arm rest 26, or both. The therapeutic support device 10 may comprise a lower back support 20 oriented between the thoracolumbar force pad 28 and the thigh rest 16. The frame 14 may be set upon a supporting surface 30, such as a floor 30, and the frame 14 may provide structure for supporting the various components of the therapeutic support device 10. The frame 14 may comprise a base 15 comprising wheels hundred and 60. One or more of the various components may be movable relative to the frame 14 to provide at least one size-adjustable area, such as the cervical treatment area 23 or the thoracolumbar treatment area 58, for receiving and supporting the user 12. The headrest 22 may be pivotable about an headrest rotation axis 96, also known herein as headrest axis 96. The headrest rotation axis 96 may be located to a front side of the back support 18. The headrest rotation axis 96 may be located to a front side of the headrest 22. The headrest rotation axis 96 may extend through an area that may be occupied by a user 12 when the user 12 may be supported by the therapeutic support device 10. FIG.51 shows a side view of the embodiment of the therapeutic support device 10 shown in FIG.49. FIG.50 shows an example of a range of movement of the headrest 22, and an example of a range of movement of the thoracolumbar force pad 28. The headrest 22 may be configured to move a head 402 of the user 12 back and forth according to a movement pattern, which may be characterized as a normal movement pattern. The headrest 22 may be moveable between a FTP 31 and a STP 33. The FTP 31 may comprise a flexion position configured to impart cervical flexion to a neck 408 of the user 12. The STP 33 may comprise an extension position configured to impart cervical extension to the neck 408 of the user 12. The headrest 22 may be moveable about an arc 35 between the FTP 31 and the STP 33. A center of rotation of the arc 35 may comprise the headrest rotation axis 96. The thoracolumbar force pad 28 may be configured to apply pressure to a thoracolumbar region of the user 12. The thoracolumbar force pad 28 may be moveable along a thoracolumbar force pad axis 29 between a FTP 41 and a STP 43. The thoracolumbar force pad axis 29 may be Z. Grajcar DKT. NO.408439-X orthogonal to a surface of the back support 18 and the thoracolumbar force pad 28 may be configured to extend from the surface of the back support 18. The FTP 41 may comprise a retracted position wherein the thoracolumbar force pad 28 may be aligned with or recessed with respect to the surface of the back support 18. The STP 43 may comprise an extended position wherein the thoracolumbar force pad 28 may extend from the surface of the back support 18 and may apply a force to a thoracolumbar region, such as the lumbar spine 446, the thoracic spine 445, or some combination thereof, of the user 12. The thoracolumbar force pad 28 may be configured for any suitable amount of movement between the FTP 41 and the STP 43. The headrest 22 may be configured for oscillation between the FTP 31 and the STP 33. The thoracolumbar force pad 28 may be configured for oscillation between the FTP 41 and the STP 43. Cyclic movement of the headrest 22 may be synchronized with cyclic movement of the thoracolumbar force pad 28. For example, as the headrest 22 and the thoracolumbar force pad 28 move back and forth along their respective paths, the headrest 22 and the thoracolumbar force pad 28 reach the FTP 31 and the FTP 41 at substantially the same time, and reach the STP 33 and the STP 43 at substantially the same time. The headrest 22 may have any suitable range of motion between the FTP 31 and the STP 33. The headrest 22 may comprise a neutral position wherein the neck 408 of the user 12 may assume a neutral orientation. The neutral position may be located between the FTP 31 and the STP 33. When the headrest 22 may be in the neutral position, the headrest 22 may be coplanar with the back support 18, wherein a support surface of the headrest 22 may be oriented on a backrest reference plane 19 aligned with the support surface of the back support 18. Movement of the headrest 22 from the neutral position to the FTP 31 may comprise a forward movement to a first side 45 of the backrest reference plane 19. Movement of the headrest 22 from the neutral position to the STP 33 may comprise a rearward movement to a second side 47 of the backrest reference plane 19. Alternatively, it is contemplated that the headrest 22 may oscillate between the FTP 31 and the STP 33 in front of or anterior to the backrest reference plane 19. Alternatively, it is contemplated that the headrest 22 may oscillate between the FTP 31 and the STP 33 in back of or posterior to the backrest reference plane 19 A range of motion of the headrest 22 used during a treatment session of the user 12 may be less than a full range of motion (e.g., arc 35) available for the headrest 22 based on mechanical, software, and other factors. The range of motion of the headrest 22 used during the treatment of the user 12 may be determined by the physical limitations of the user 12. As one skilled in the art would know, cervical fusion, cervical discectomy, cervical trauma, neck trauma, prior neck surgery, etc. may limit range of motion for the user number 12. Z. Grajcar DKT. NO.408439-X The headrest 22 may be rotatable about an headrest rotation axis 96, and the headrest rotation axis 96 may be positioned at a location that may allow the headrest 22 to comfortably support a head 402 of the user 12 throughout the range of motion of the headrest 22. The headrest rotation axis 96 may extend through the cervical treatment area 23 that may be occupied by the user 12 supported by the therapeutic support device 10. The headrest rotation axis 96 may be oriented just under a chin of the user 12. The headrest rotation axis 96 may intersect the neck 408 of the user 12. The headrest rotation axis 96 may be oriented to a first side 45, also characterized as a front side or anterior side, of the backrest reference plane 19. The headrest 22 may define a headrest reference plane 27, for example aligned with a supporting surface of the headrest 22. The headrest reference plane 27 may be coplanar with the backrest reference plane 19 when the headrest 22 may be in the neutral position. The headrest rotation axis 96 may be located to the first side 49 of the headrest reference plane 27. A body of the user 12 may define a natural rotation axis for the head, and the headrest rotation axis 96 may be collinear with the natural rotation axis. The therapeutic support device 10 may comprise several different mechanisms for adjustment. The therapeutic support device 10 may be adjustable to move the headrest 22 with respect to the thigh rest 16. The location of the headrest rotation axis 96 of the headrest 22 may be adjustable with respect to the thigh rest 16. The location of the back support 18 may be adjustable with respect to the thigh rest 16. The location of the thoracolumbar force pad 28 may be adjustable with respect to the thigh rest 16. The location of the thoracolumbar force pad 28 may be adjustable with respect to the headrest 22 and / or the headrest rotation axis 96 of the headrest 22. The therapeutic support device 10 may be adjusted to ease entry of the user 12 into the therapeutic support device 10 and exit of the user 12 from the therapeutic support device 10. The therapeutic support device 10 may comprise a TRAM 38 configured to move the thigh rest 16 with respect to the base 15. The TRAM 38 may be configured to move several portions of the therapeutic support device 10 collectively with respect to the base 15. The TRAM 38 may be configured to move the thigh rest 16, the back support 18, the thoracolumbar force pad 28, and the headrest 22 collectively with respect to the base 15. Additionally, the TRAM 38 may move the leg rest 24 and the arm rest 26 collectively with the thigh rest 16 with respect to the base 15. FIGS.49 and 50 show an embodiment of the therapeutic support device 10 in a treatment orientation. The user 12 may be on the therapeutic support device 10 in the treatment orientation during a treatment session. FIGS.51 and 52 show the embodiment of the therapeutic support device 10 in an entry orientation. The user 12 may be on the therapeutic support device 10 in the entry position during entry of the user 12 onto the therapeutic support device 10, exit of the user 12 from the therapeutic support device 10, or both. Z. Grajcar DKT. NO.408439-X FIGS.53-56 show additional views of the embodiment of the therapeutic support device 10 in a treatment orientation, with additional components visible. An angle of the thigh rest 16 with respect to the supporting surface 30 may change between the entry orientation and the treatment orientation. The thigh rest 16 may be parallel with the supporting surface 30 in the entry orientation. The thigh rest 16 may be non-parallel with the supporting surface 30 in the treatment orientation. An angle between the thigh rest 16 and the back support 18 may change between the entry orientation and the treatment orientation. An angle between the thigh rest 16 and the leg rest 24 may change between the entry orientation and the treatment orientation. The frame 14 may comprise the base 15 and at least one column member 17 may support various components of the therapeutic support device 10. The at least one column member 17 may support the thigh rest 16 and the back support 18. The back support 18 may support the headrest 22. The thigh rest 16 may support the leg rest 24. The frame 14 may comprise a hinge 44, and the thigh rest 16 may be pivotable about the hinge 44. The back support 18 may be pivotable about the hinge 44. The at least one column member 17 may support the hinge 44. The thigh rest 16 may comprise a cushion, a thigh rest frame 25, or both. The thigh rest frame 25 may be pivotally engaged with the hinge 44. The TRAM 38 may be attached to the base 15 at a first point 40 and may be attached to the thigh rest frame 25 at a second point 42. The TRAM 38 may be configured to move the first point 40 with respect to the second point 42. The TRAM 38 may be configured to pivot the thigh rest 16 about the hinge 44 with respect to the base 15. Adjustment of the TRAM 38 may collectively rotate the thigh rest 16, the back support 18, the headrest 22, the leg rest 24 and, the arm rest 26 about the hinge 44 with respect to the base 15. The leg rest 24 may comprise a cushion, a leg rest frame 55, or both. The leg rest frame 55 may be attached to the thigh rest frame 25. The leg rest 24 may be configured to pivot with respect to the thigh rest 16 about a leg rest axis 57. The leg rest frame 55 may be attached to the thigh rest frame 25 by a hinge 126 (see FIGS.54 and 59). A LRAM 120 may be configured to move the leg rest 24 with respect to the thigh rest 16. The LRAM 120 may be attached to the thigh rest frame 25 at a first point 122 and may be attached to the leg rest frame 55 at a second point 124. The LRAM 120 may be configured to move the first point 122 with respect to the second point 124. The leg rest 24 may comprise a first orientation with respect to the thigh rest 16 when the therapeutic support device 10 may be in an entry orientation and a second orientation with respect to the thigh rest 16 when the therapeutic support device 10 may be in a treatment orientation. An angle between a surface of the thigh rest 16 and a surface of the leg rest 24 in the entry orientation may be different from the angle in the treatment orientation. Z. Grajcar DKT. NO.408439-X The therapeutic support device 10 may comprise a BRAM 50 configured to move the back support 18 with respect to the thigh rest 16. The BRAM 50 may be configured to change an angle between the thigh rest 16 and the back support 18. The BRAM 50 may be configured to pivot the back support 18 about the hinge 44. The back support 18 may comprise a cushion, a back frame 37, or both. The back frame 37 may be configured to pivot about the hinge 44 with respect to the thigh rest 16. The back frame 37 may be configured to pivot about the hinge 44 with respect to the base 15. The BRAM 50 may be attached to the thigh rest frame 25 at a first point 51 (see FIG.52) and may be attached to the back frame 37 at a second point 53. The BRAM 50 may be configured to move the first point 51 with respect to the second point 53. The headrest 22 may be supported by the back frame 37. The thoracolumbar force pad 28 may be supported by the back frame 37. The lower back support 20 may be supported by the back frame 37. Adjustment of the BRAM 50 may move the headrest 22, thoracolumbar force pad 28, the lower back support 20 alone or in any combination with respect to the thigh rest 16, along with the back support 18. The therapeutic support device 10 may comprise a HRLAM 34 configured to move the headrest 22, for example movement with respect to the thigh rest 16. The HRLAM 34 may be configured to move the headrest rotation axis 96 of the headrest 22. The back frame 37 may comprise a first portion 61 moveable with respect to a second portion 63. The first portion 61 may be engaged with the hinge 44. The first portion 61 may support the second portion 63 of the back frame 37. The second portion 63 may support the headrest 22. The HRLAM 34 may be configured to move the second portion 63 along a second portion movement axis 39. The second portion movement axis 39 may be oriented in a radial direction of the hinge 44. The second portion movement axis 39 may be linear. The HRLAM 34 may be attached to the first portion 61 at a first point 52 and may be attached to the second portion 63 at a second point 54. The HRLAM 34 may be configured to move the first point 52 with respect to the second point 54. The back frame 37 may comprise one or more track 56, and the second portion 63 may move along the track 56 with respect to the first portion 61. The track 56 may comprise a linear guide member, for example comprising roller bearings. The second portion 63 of the back frame 37 may support the back support 18. The back support 18 may move collectively with the headrest 22 when the HRLAM 34 may be adjusted. The arm rest 26 may be supported by the second portion 63 of the back frame 37. The arm rest 26 may move collectively with the headrest 22 when the HRLAM 34 may be adjusted. In some embodiments, the arm rest 26 may comprise a connection member 132 (see FIG.54) extending between the back frame 37 and the arm rest 26. The arm rests 26 may be fixed and unmovable Z. Grajcar DKT. NO.408439-X with respect to the back frame 37. The arm rests 26 may be moveable pivotable about a central axis of the connection member 132. The lower back support 20 may be attached to the first portion 61 of the back frame 37. The HRLAM 34 may move the headrest 22 and back support 18 between the FTP 31 and the STP 33. The HRLAM 34 may be configured to adjust the therapeutic support device 10 according to the body of the user 12. A location of the thoracolumbar force pad 28 may be adjustable with respect to the headrest 22. The back frame 37 may comprise a third portion 65 configured to support the thoracolumbar force pad 28. The third portion 65 may be configured to move along a linear axis 59. The linear axis 59 may be parallel to the second portion movement axis 39 of the back support 18, the headrest 22, or both. The third portion 65 may be configured to move with respect to the second portion 63. The third portion 65 may be configured to move with respect to the first portion 61. The second portion 63 may support the third portion 65. The therapeutic support device 10 may comprise a TFPLAM 78 configured to move the thoracolumbar force pad 28 with respect to the headrest 22. The TFPLAM 78 may be configured to move the third portion 65 of the back frame 37 with respect to the second portion 63. The TFPLAM 78 may be attached to the second portion 63 at a first point 71 and may be attached to the third portion 65 at a second point 73. The TFPLAM 78 may be configured to move the first point 71 with respect to the second point 73. The TFPLAM 78 may be configured to move the third portion 65 along a linear axis. The linear axis 59 may be oriented in a radial direction of the hinge 44. The third portion 65 of the back frame 37 may comprise a bracket that may be slidably engaged with the second portion 63. The third portion 65 may be attached to the second portion 63 via one or more tracks 72, and the third portion 65 may move along the track 72 with respect to the second portion 63. A track 72 may comprise a linear guide member. The track 72 may comprise comprising roller bearings. As mentioned previously, the thoracolumbar force pad 28 may be moveable along a thoracolumbar force pad axis 29 between a FTP 41 and a STP 43 (see e.g., FIG.50). The thoracolumbar force pad 28 may extend farther into the thoracolumbar treatment area 58, which is size-adjustable, when the thoracolumbar force pad 28 may be in the STP 43. The TFPAM 64 may be supported by the third portion 65 of the back frame 37. An output (e.g., output shaft) of the TFPAM 64 may be attached to a plate 60, and the TFPAM 64 may be configured to move the plate 60. The thoracolumbar force pad 28 may be attached to the plate 60. The TFPAM 64 may be aligned with a center of the thoracolumbar force pad 28. The therapeutic support device 10 may comprise one or more guide support 80 configured to support the thoracolumbar force pad 28. A guide support 80 may be attached to the third portion 65. The Z. Grajcar DKT. NO.408439-X guide support 80 may comprise a linear bearing block configured to guide a connection member 82 along its longitudinal axis. The connection member 82 may be attached to the plate 60, the thoracolumbar force pad 28, or both. The longitudinal axis of the connection member 82 may be oriented parallel to the thoracolumbar force pad axis 29. A guide support 80 may be configured to support a connection member 82 and another of the guide support 80b may be configured to support a connection member 82b in a similar manner. The TFPAM 64 may be located between the guide support 80 and the guide support 80b. FIGS.56-59 show the embodiment of the therapeutic support device 10 of FIG.49 in additional orientations with additional components visible that may be related to movement of the headrest 22. The therapeutic support device 10 may comprise a headrest actuation mechanism 98 configured to move the headrest 22 with respect to the back support 18. The headrest actuation mechanism 98 may be configured to move the headrest 22 about the headrest rotation axis 96. The headrest 22 may be supported by a headrest frame 94 that may be attached to the back frame 37. The headrest frame 94 may be attached to the second portion 63 of the back frame 37. The headrest frame 94 may extend from the back frame 37 to the headrest rotation axis 96, and the headrest frame 94 may support the headrest 22 at the headrest rotation axis 96. The headrest frame 94 may comprise a first portion extending from the back frame 37 to the headrest rotation axis 96 and further may comprise a second portion 95 extending from the back frame 37 to the headrest rotation axis 96. The first portion of the headrest frame 94 may be located to a first side of the headrest 22, and the second portion 95 may be located to a second side of the headrest 22. The headrest 22 may comprise a bracket 91 configured to support a cushion 21. The bracket 91 may be supported by the headrest frame 94 and configured to pivot about the headrest rotation axis 96. The first portion and the second portion 95 of the headrest frame 94 each support an axle member 93, and each axle member 93 may support the bracket 91. Each of the axle member 93 may be aligned on the headrest rotation axis 96. The bracket 91 may comprise a first portion 97 and an arm 92, which may be one or more. The first portion 97 may be configured to support the cushion 21. The arm 92 may extend to the headrest rotation axis 96 and may engage the headrest frame 94, the axle member 93, or both. The arm 92 may engage the first portion of the headrest frame 94 and another of the arm 92 engages the second portion 95 of the headrest frame 94. The first portion 97 of the bracket 91 may be oriented behind the cushion 21 and the arm 92 extend in front of the cushion 21. The headrest actuation mechanism 98 may be engaged with the bracket 91 and configured pivot the bracket 91 about the headrest rotation axis 96. The headrest actuation mechanism 98 may be engaged with the arm 92 of the bracket 91. Z. Grajcar DKT. NO.408439-X The headrest actuation mechanism 98 may be attached to the headrest frame 94 and supported by the headrest frame 94. The headrest actuation mechanism 98 may comprise a motor configured to rotate a driveshaft 102. An axis 103 of the driveshaft 102 may be offset from the headrest rotation axis 96 of the headrest 22. A drive mechanism 101 may be configured to transfer force from the driveshaft 102 to the headrest 22 to cause movement about the headrest rotation axis 96. The driveshaft 102 may be engaged with a crank arm 104. The crank arm 104 may be oriented in a radial direction of the driveshaft 102. The driveshaft 102 may be configured to rotate the crank arm 104 about the axis 103. A drive linkage 90 extends between the crank arm 104 and the bracket 91. The drive linkage 90 may be pivotally attached to the crank arm 104 at a first point 106 that may be offset from the axis 103. The drive linkage 90 may be pivotally attached to the bracket 91 at a second point 110 that may be offset from the headrest rotation axis 96. The driveshaft 102 may be configured to move the first point 106 along an arcuate path about the axis 103. The drive linkage 90 may be configured translate force from the headrest actuation mechanism 98 to move the bracket 91 about the headrest rotation axis 96 in the same manner that the crank arm 104 rotates about the driveshaft 102 of the headrest actuation mechanism 98. Movement of the second point 110 about the headrest rotation axis 96 may be similar to movement of the first point 106 about the axis 103. The drive linkage 90 may comprise a curvature, for example avoid interference with the headrest rotation axis 96 or for aesthetic purposes. The headrest actuation mechanism 98 may be oriented on the headrest rotation axis 96 of the headrest 22 (not shown). The driveshaft 102 may be aligned on the headrest rotation axis 96 and configured to rotate the headrest 22 about the headrest rotation axis 96. The driveshaft 102 may be directly engaged to the bracket 91. The headrest actuation mechanism 98 may comprise a rotational motor. The headrest actuation mechanism 98 may comprise a stepper motor, such as a hybrid rotary stepper motor available from Dings’ Motion USA, Morgan Hill, CA. The headrest actuation mechanism 98 may comprise a gearbox, for example configured to reduce speed and increase torque. FIGS.60 and 61 show the embodiment of the therapeutic support device 10 shown in FIG.49 with the headrest 22 in the FTP 31. FIG.51 depicts the user 12 during treatment with the therapeutic support device 10 in the FTP 31. The FTP 31 of the headrest 22 may comprise a flexion position configured to impart cervical flexion to the neck 408 of the user 12. The thoracolumbar force pad 28 may be in the FTP 41 when the therapeutic support device 10 may be in the FTP 31. The thoracolumbar force pad 28 might not apply a force to the lumbar region of the user 12 when the therapeutic support device 10 may be in the FTP 31. Z. Grajcar DKT. NO.408439-X As shown in FIG.51, in some embodiments, the headrest rotation axis 96 of headrest 22 movement may extend through a cervical treatment area 23 that may be occupied by the user 12 when supported by the therapeutic support device 10. The headrest rotation axis 96 may be configured to extend through a neck 408 of the user 12. FIGS.62 and 63 show the embodiment of the therapeutic support device 10 shown in FIG.49 with the headrest 22 in the STP 33. FIG.63 depicts the user 12 during treatment with the therapeutic support device 10 in the second orientation. The STP 33 of the headrest 22 may comprise an extension position configured to impart cervical extension to the neck 408 of the user 12. The thoracolumbar force pad 28 may be in the STP 43 when the therapeutic support device 10 may be in the second orientation. The thoracolumbar force pad 28 may be configured to apply a force to the lumbar region of the user 12 when the therapeutic support device 10 may be in the second orientation. When the therapeutic support device 10 may be in a treatment orientation, the user 12 may be positioned in a zero-gravity position. The zero-gravity position means that the body of the user 12 may be in a neutral posture while the feet may be elevated in alignment with the heart. In the zero-gravity position, the torso 403 of the user 12 and the thigh of the user 12 may be at equal angles from the hip, the upper body may be elevated, the knees 416 may be bent, and / or the legs may be raised to about level of the chest 404. In this position, the spine may be in a relatively stress-free position, the angle of the head may be such that a tongue of the user 12 may be at a normal position, so breathing may be easier, and / or with the legs raised slightly, blood flows more easily through the of the user 12. For some user 12s, the zero-gravity position may decrease stress, lower blood pressure, relax the brain, or any combination of the three. When the therapeutic support device 10 may be in a treatment orientation, the user 12 may be positioned in a Trendelenburg position with head 402 of the user 12 down relative to the feet of the user 12. In this position, the user 12 may be laid face up on a surface with a reverse incline, positioning the body of the user 12 on a reverse incline with the feet being positioned above the head. Control System The therapeutic support device 10 may comprise a Main Control Unit (also known herein as MCU) 89 configured to control operation of the various moving portions of the therapeutic support device 10, such as the TRAM 38, the BRAM 50, the LRAM 120, the HRLAM 34, the TFPLAM 78, the headrest actuation mechanism 98 and / or the TFPAM 64. The therapeutic support device 10 may comprise a primary BUS HUB 85 configured to house the MCU 89 (see FIG.50). The BUS HUB 85 may be attached to the thigh rest frame 25. In some embodiments, at Z. Grajcar DKT. NO.408439-X least one cable (which may not be not illustrated) may extend between the primary BUS HUB 85 and each of the TRAM 38, the BRAM 50, the LRAM 120, the HRLAM 34, the TFPLAM 78, the headrest actuation mechanism 98, the TFPAM 64, and the MCU 89 may be operatively engaged with each of the TRAM 38, the BRAM 50, the LRAM 120, the HRLAM 34, the TFPLAM 78, the headrest actuation mechanism 98, the TFPAM 64, when present. The therapeutic support device 10 may comprise the primary BUS HUB 85 that is primary and a secondary BUS HUB 87 that is secondary (see e.g. FIG.51). The secondary BUS HUB 87 may comprise an expansion HUB configured to provide additional cable ports. There may be more than one of the secondary BUS HUB 87. A secondary BUS HUB 87 may be attached to the back frame 37. The MCU 89 may be configured to receive commands from a control unit 115 (see FIG.50), such as a tablet, computer or the like. The control unit 115 communicates wirelessly with the MCU 89, for example using Bluetooth and / or Wi-Fi wireless communication. The control unit 115 communicates with the MCU 89 using physical connections such as cables. When the therapeutic support device 10 may be in a treatment orientation, the user 12 may be positioned in a reverse Trendelenburg position with head 402 of the user 12 raised above the feet of the user 12. The user 12 may be laid face up on a surface with a positive incline, positioning the body on an incline with the head being positioned above the feet. The person may be positioned at an angle of about 15oto about 20o. The person may be positioned at an angle of about 30oto about 40o. The therapeutic support device 10 may be configured to operate according to a cyclical oscillatory motion between the first position and the second position. The first position may be shown in FIG.63. In the first position, the headrest 22 may be extended towards the floor 30 and the thoracolumbar force pad 28 may be extended. The second position may be shown in FIG.61. In the second position, the headrest 22 may be flexed and the thoracolumbar force pad 28 may be retracted. The user 12 breathing in gaited in synchronization with the cyclical oscillation of the therapeutic support device 10. The user 12 may inhale during the transition from the second position (FIG.61) to the first position (FIG.63), and may exhale during the transition from the first position to the second position. The inhale portion of the cycle and the exhale portion of the cycle may have different period lengths. The transition from the second position to the first position (e.g., inhale) may comprise a first period of time and the transition from the first position to the second position (e.g., exhale) may comprise a second period of time. The second period of time may be longer than the first period of time. The second period of time may range from 1.5x to 2x the first period of time. The inhale cycle and movement from the second position to the first position may comprise a first period of time of 4 to 8 seconds. The exhale cycle and Z. Grajcar DKT. NO.408439-X movement from the first position to the second position may comprise a second period of time of 6 to 12 seconds. The inhale cycle and movement from the second position to the first position may be 5 seconds and the exhale cycle and movement from the first position to the second position may be 7 seconds. A full oscillation of movement may comprise beginning in the second position (FIG.61), a first movement transitioning to the first position (FIG.63) and a second movement returning to the second position. The first movement of the oscillation may comprise 35%-45% of the time of the full oscillation, and the second movement of the oscillation may comprise 55%-65% of the time of the full oscillation. The headrest 22 may comprise a range of motion and the thoracolumbar force pad 28 may comprise a range of motion. A treatment motion used during treatment may be less than the full range of motion that the headrest 22, thoracolumbar force pad 28, or both may be capable. The user 12 may be evaluated for a comfortable range of motion, and limitations at less than the full the range of motion of the headrest 22, the thoracolumbar force pad 28, or both may be used. FIG.64 shows another embodiment of the therapeutic support device 10 in an entry orientation. FIG.65 shows the therapeutic support device 10 of FIG.64 in a treatment orientation. FIG.66 shows the therapeutic support device 10 of FIG.64 in the treatment orientation with a HRLAM 34 in an extended orientation. Similar reference characters may be used to indicate similar features between the embodiments. The TFPLAM 78 may be configured to move the third portion 65 of the back frame 37 with respect to the first portion 61. The TFPLAM 78 may be attached to the first portion 61 at a first point 75 and may be attached to the third portion 65 at a second point 73. The first portion 61 of the back frame 37 may comprise one or more guide slots 111, and at least one component of the thoracolumbar force pad 28, may move in the guide slot 111 as the TFPLAM 78 may move the third portion 65. FIG.66 shows an embodiment of the therapeutic support device 10 with the HRLAM 34 in an extended orientation. The HRLAM 34 may be configured to move the headrest 22 and headrest rotation axis 96, for example with respect to the thigh rest 16, to the first portion 61 of the back frame 37, or both. The first portion 61 of the back frame 37 may comprise a guide member 117, of at least one, and the second portion 63 of the back frame 37 may comprise at least one block 119 configured to slide along the guide member 117. FIG.67 shows another embodiment of a drive mechanism 101 configured to transfer force from a driveshaft 102 to the headrest 22 to cause movement of the headrest 22 about the headrest rotation axis 96. The drive mechanism 101 may comprise a belt 125 that may be operatively engaged with the headrest actuation mechanism 98 and with the headrest 22. A driveshaft pulley Z. Grajcar DKT. NO.408439-X 127 may be oriented between a driveshaft 102 of the headrest actuation mechanism 98 and the belt 125. A headrest pulley 129 may be oriented between the belt 125 and the headrest 22. The headrest pulley 129 may be oriented on the headrest rotation axis 96. The axle member 93 may be engaged with the headrest pulley 129 and the headrest 22. The driveshaft 102 may rotate back and forth, and the headrest pulley 129 and the headrest 22 may rotate back and forth in a similar manner. A tensioner 131 may be provided to maintain tension on the belt 125. TILT TABLE A tilt table actuation mechanism may be configured to rotate the headrest, the backrest, the thigh rest, and the leg rest with respect to the base into the FTP and the STP. The maximum down position of the head 402 of the user 12 may be the FTP, and the maximum up position of the head 402 of the user 12 may be the STP. The tilt table actuation mechanism may be configured to move the headrest, the backrest, the thigh rest, and the leg rest with respect to the base between the FTP and the STP during each treatment cycle during the treatment session. An upper body tilt table actuation mechanism may be configured to rotate the headrest and the backrest with respect to the thigh rest and the leg rest into the FTP and the STP. The upper body tilt table actuation mechanism may be configured to rotate the headrest and the backrest with respect to the thigh rest and the leg rest into the FTP and the STP during each treatment cycle during the treatment session. A zero-gravity actuation mechanism may be configured to rotate the leg rest, the thigh rest, the backrest, the force pad, and the headrest collectively with respect to the base into the FTP and the STP. The zero-gravity actuation mechanism may be configured to rotate the leg rest, the thigh rest, the backrest, the force pad, and the headrest collectively with respect to the base into the FTP and the STP during each treatment cycle during the treatment session. In the zero- gravity position, the spine may be in a relatively stress-free position, the angle of the head may be such that a tongue of the user 12 may be at a normal position, so breathing may be easier, and / or with the legs raised slightly, and blood flows more easily through the body of the user 12. For some subjects, the zero-gravity position will decrease stress, lower blood pressure, and / or relax the brain. One or more of the adjustment mechanisms may be swapped out for actuation mechanism with a heavier duty cycle in any of the CSF pump device 10 disclosed herein. STIMULATING THE USER 12 The CSF pump device 10, which comprises one or more of the CSF pump 100 disclosed, may be configured to stimulate the CNS of the user 12, and so may be considered a CNS stimulation Z. Grajcar DKT. NO.408439-X device. Stimulation of the CNS may comprise movement of the user 12. In addition to movement of the user 12 as disclosed to improve glymphatic clearance, other stimulation of the user 12 may be provided to induce improved glymphatic clearance through low brain wave activity that occurs during sleep, meditation, or similar mental state. During low brain wave activity, blood pressure of the user 12 drops that allows the periarterial and perivenous channels that carry CSF to the brain parenchyma to open more that in turn results in increased CSF flow. A visual stimulation device may be configured to stimulate the user 12, such as head set with a visual display, computer display, television display, etc., as shown in FIG.71. The headset may be an augmented reality or virtual reality device such as Apple brand Vision Pro or Meta Brand Quest 3. Apple brand Vision Pro may be a product of Apple. Meta Brand Quest 3 may be a product of Meta. The visual display device may be coupled to a visual display control device, such as a general purpose or a purpose built device that may be configured to display visual stimulation to achieve the desired brain wave activity. The display device may be coupled to the visual display control device by wire or wirelessly, as described herein. The visual stimulation may be a flicker of visible light. The visual stimulation may be a series of flashes or pulses with a frequency that may calm the user 12 and induces desired brain wave activity, such as slow brain wave activity. The visual stimulation may be one or more in a series of images that calms the user 12, such as pictures of scenery, friends, family, etc. of devices may be used of course. An auditory stimulation device may be configured to stimulate the user 12, such as a headset with over the ear or in ear headphones, as shown in FIG.75. JBL-Live 660NC Bluetooth wireless headphones may be a product of JBL Harman may be an example of an auditory stimulator. The auditory device may be coupled to an auditory control device, such as a computer or a purpose built device that may be configured to provide auditory stimulation to achieve the desired brain activity. The auditory device may be coupled to the auditory control device by wire or wirelessly, as described herein. The auditory stimulation may be music or other sounds. The auditory information may calm the user 12 to induce slow brain wave activity. Other devices may be used of course. An electromagnetic stimulation device may be configured to stimulate the user 12. A tactile stimulation device may be configured to tactilely stimulate the user 12 from a tactile stimulation device, such as an electromagnetic energy source like TENS 7000 Digital TENS Unit, as shown in FIG.71. TENS 7000 Digital TENS Unit may be a product of TENS 7000. The tactile stimulation may calm the user 12. Transcranial magnetic stimulation may be a noninvasive form of brain stimulation in which a changing magnetic field may be used to induce an electric current at a specific area of the brain through electromagnetic induction. During the procedure, a magnetic coil may be positioned at the head of the person receiving the treatment, and the Z. Grajcar DKT. NO.408439-X magnetic coil may be then connected to a pulse generator, or stimulator, that delivers electric current to the coil. Transcranial magnetic stimulation may be achieved by quickly discharging current from a large capacitor into a coil to produce pulsed magnetic fields between 2 and 3 Tesla in strength. Magstim 200^2 TMS by Magtim may be an example of transcranial magnetic stimulation device. Other devices may be used of course. The visual stimulation device, the auditory stimulation device, and the tactile stimulation device, along with the computer or the purpose built device may be powered by a power source, such as battery or mains or other suitable power source. Stimulation of the user 12 may be provided by one or more of the stimulation devices disclosed. The wireless connections may be Bluetooth technology, which is a short-range wireless technology standard that may be used for exchanging data between fixed and mobile devices over short distances and building personal area networks. The Institute of Electrical and Electronics Engineers (IEEE) standardized Bluetooth as IEEE 802.15.1. The wireless connections may be Wi-Fi technology, which is a family of wireless network protocols based on the IEEE 802.11 family of standards, which may be commonly used for local area networking of devices and Internet access, allowing nearby digital devices to exchange data by radio waves. The wired connections may be Ethernet technology, which is a family of wired computer networking technologies commonly used in local area networks (LAN), metropolitan area networks (MAN) and wide area networks (WAN). Ethernet was first standardized in 1983 as IEEE 802.3. Power over Ethernet (PoE) that describes any of several standards or ad hoc systems that pass electric power along with data on twisted-pair Ethernet cabling may be used for stimulation, monitoring, and control systems. The wired connections may be simply direct wired connections of any suitable type known to one skilled in the art. The wired and wireless connections may be used to couple any parts or components of the CSF pump 100s, CSF pump devices 10, stimulation devices, monitoring devices, and control systems, and anything else disclosed in this application. MONITORING THE USER 12 AND THE CSF PUMP 100 FIG.72 shows the user 12 coupled to sensors for measuring and recording respiration cardiac, and brain activity of the user 12, all of which may be optional. Respiration activity of the user 12 includes respiration rate, pulse oximetry, etc. The respiration activity may be sensed and recorded. A respiration activity monitor may be configured to sense respiration activity of the user 12. The respiration activity monitor may be configured to provide the information regarding respiration activity that may then be recorded. Z. Grajcar DKT. NO.408439-X An example of a respiration activity monitor may be Pulse XS pro may be a pulse oximeter that may be a product of Oxiline, but other devices may be used of course. Another example of a respiration activity monitor may be Capnostream 35 portable respiratory monitor provides monitoring of CO2, SpO2, pulse rate, and respiration rate and may be a product of Nellcor. The information obtained may be recorded in a database for further analysis, usage, etc. Cardiac activity of the user 12 includes pulse, pulse rate, blood pressure, electrocardiogram, etc. The cardiac activity may be sensed and recorded. A cardiac activity monitor may be configured to sense cardiac activity of the user 12. The cardiac activity monitor may be configured to provide the information regarding cardiac activity that may then be recorded. An example of a cardiac activity monitor may be Complete Wireless Upper Arm Blood Pressure Monitor and EKG, or similar, may be used to record cardiac activity, but other devices may be used of course. Complete Wireless Upper Arm Blood Pressure Monitor and EKG may be a product of Omron. Other senses for recording cardiac activity are disclosed elsewhere and known to one skilled in the art. Brain activity includes brain wave activity, level of alertness, level of sleep, etc. Brain sensor and recording device, such as Trackit T4A ambulatory EEG, or similar, records brain activity. Trackit T4A ambulatory EEG may be a product of Nihon Kohden Corporation. Electroencephalography (EEG) may be a method to record an electrogram of the spontaneous electrical activity of the brain. The frequencies of brain wave activity recorded by EEG may be subdivided into various groups: delta (0.5–4 Hz or more generally 4 Hz or less.), theta (4–7 Hz), alpha (8–13 Hz), and beta (13–30 Hz). Delta and theta waves might not be seen in wakefulness in the user 12 that may be normal. Alpha waves may be observed when a person may be in a state of relaxed wakefulness and may be mostly prominent over the parietal and occipital lobes of the brain. During intense mental activity, beta waves may be more prominent in frontal areas and other regions of the brain. EEG apparatus may be applied to scalp on the skull of the user 12. A skullcap with EEG electrodes may be used. EEG electrodes may be placed individually in a more traditional fashion. Other suitable sensors, besides those specifically mentioned, may be of course available to monitor respiration activity, cardiac activity, and brain wave activity for sensing and recording the respective activities. The information obtained from the various sensors may be recorded in a database and use for further analysis, feedback for the user, etc. The CSF pump 100 activity may be monitored and recorded. The proximity sensor 514 may be configured to sense activity of the CSF pump 100. The proximity sensor 514 may be configured to provide the information regarding activity of the CSF pump 100 that may then be recorded. The proximity sensor 514 may be configured to send a stop signal to stop the CSF Z. Grajcar DKT. NO.408439-X pump 100 activity immediately. The proximity sensor 514 may be configured to send a stop signal to stop the CSF pump 100 activity at the end of the next treatment cycle. The proximity sensor 514 may be configured to stop the CSF pump 100 activity when the CSF pump 100 next reaches the first treatment position. The proximity sensor 514 may be configured to stop the CSF pump 100 when the CSF pump 100 next reaches the second treatment position. The CSF pump 100 may be configured with an emergency stop button. The activation of the emergency stop button may be configured to immediately stop the CSF pump 100 activity. The emergency stop device may be configured to be operated by the user 12. The emergency stop device may be configured to be operated by the operator assisting the user 12 in the use of the CSF pump 100. The emergency stop button may connect to the network. The emergency stop button may connect only to the CSF pump device. The CSF pump 100 may be configured with a stop button easily accessible to the user 12 while using the CSF pump 100. The activation of the stop button may be configured to immediately stop the CSF pump 100 activity. The stop button may be configured to stop the CSF pump 100 when the CSF pump 100 next reaches the first treatment position. The stop button may be configured to stop the CSF pump 100 when the CSF pump 100 next reaches the second treatment position. The wired and wireless connections disclosed herein and otherwise known to one skilled in the art may be used to couple any parts of the CSF pump 100s, CSF pump devices, stimulation devices, monitoring devices, and control systems, and anything else disclosed in this application, as discussed hereinabove. STIMULATION AND MONITORING DATABASE 526S The stimulation database 526 comprises information for one or more of the stimulation devices, such as but not limited to the CSF pump device 10, the visual stimulation, the auditory stimulation, the electromagnetic stimulation the tactile stimulation. The monitoring database 526 comprises information for one or more of the monitoring devices, such as but not limited to the CSF pump device 10 monitor, the respiration activity monitor, the cardiac activity monitor, and the brain wave activity monitor. User age, height, sitting height, weight, body mass index, etc. be recorded in the database for use with the individual user or with appropriate privacy controls to develop anonymous operational parameters for the CSF pump device 10. The information is stored in the database to be used during a treatment session, before and after a treatment session for the user. The database information may be retrieved at future Z. Grajcar DKT. NO.408439-X treatment sessions for usage. Privacy concerns can be addressed so that information is not shared between different subjects and only authorized operators are allowed to access the information. CONTROL SYSTEM FOR THE CSF PUMP DEVICE 10, AND STIMULATING AND MONITORING THE USER 12 So far, we have disclosed the CSF pump device 10 for changing the fluid dynamics of the cerebrospinal fluid in the CSF system of the user 12. To recap, by changing the fluid dynamics, the CSF pump 100 may be configured to change the pressure and therefore the flow and flux of the CSF in the CSF system. The change in the flow and flux of the cerebrospinal fluid change the glymphatic clearance of the user 12. Improving the glymphatic clearance will typically involve increasing the CSF pressure, flow, and flux; and glymphatic clearance. Improving the glymphatic clearance for a given user 12 may decrease the glymphatic clearance, depending on the situation. Therefore, the CSF pump 100s can be viewed to improve or optimize the glymphatic clearance. The CSF pump device 10 may be configured to change a volume of the CSF in the CSF system. The CSF device may be configured to decrease a volume of the CSF in the CSF system. The CSF pump device 10 may be configured to increase a volume of the CSF in the CSF system. FIG.77 shows a schematic representation of a control system that comprises the CSF pump device 10, the other stimulation devices, and the monitoring devices. Any of the CSF pump device 10s (which may be one or more CSF pump) disclosed may be used with the control system, the other stimulation devices, and the monitoring devices. Any of the other stimulation devices disclosed may be used with the control system. Any of the monitoring devices may be used with the control system. A single movement of the CSF pump 100 from the FTP to the STP will establish a pressure gradient and therefore flow and flux of the cerebrospinal fluid. However, if only a single movement of the CSF pump 100 from the FTP to the STP may be performed, the effects of the peristaltic pump might not be maintained. Only effects of the hydrostatic pump will be maintained over time in movement of the CSF pump 100 from the FTP to the STP. However, by repeatedly moving the CSF pump 100 to and from the FTP, the CSF pump 100 may establish and maintain the peristaltic pressure on the cerebrospinal fluid. In addition, the hydrostatic pressure may change over time with movement of the CSF pump 100 from the FTP to the STP. And so, the change in the CSF pressure, flow, and flux; and glymphatic clearance may be maintained for improved CSF flow and flux; and glymphatic clearance; and changed volume of CSF in the CSF system. The repeated movement of the CSF pump 100 may be from the FTP to the STP and from the STP to the FTP. In other words, the repeated movement of the CSF may be back and forth between the FTP to the STP. The optional repeated movement may be viewed as oscillatory. Z. Grajcar DKT. NO.408439-X An actuator may be configured to control the CSF pump device 10 and the one or more of the CSF pump 100s of the CSF pump device 10. The control system may be configured to control the actuator. The control system includes one or more database 526s to facilitate efficiently setting up the user 12 within the CSF pump device 10 and recalling the settings obtained for the user 12 within the CSF pump device 10 at a later time. The stimulation settings that induce slow brain activity may be recalled and implemented in the upcoming treatment session. The settings for the FTP, the STP, etc. may be considered a prescription that may be established on fitting the user 12 in the CSF pump device 10. A CSF pump device prescription database 526 for subjects 12 may be provided with an example of settings for FTP, STP, etc. for a user 12 of a given age, height, sitting height, weight, body mass index, etc. The settings for the FTP, the STP, etc. obtained in fitting any of the subjects in the CSF pump device 10 may be stored in a user 12 prescription database 526 for the subjects 12. The user 12 may be identified by an indicium of any type within the database 526 of fitting prescriptions for the subjects. The indicium includes name, birth date, clinical identification, etc. The indicium may be worn by the user 12 such as on a hospital bracelet, clinical bracelet, etc. Privacy between subjects may be maintained, so that one user 12 does not learn the details of another user 12. A therapeutic response database 526 of the user 12 may be provided. The therapeutic response database 526 of the user 12 includes sensor information from the respiration sensor, the cardiac sensor, the brain sensor, motor sensors, other sensors, or any combination thereof that may be collected during use of the CSF pump device 10 on the user 12, and before or after use of the CSF device on the user 12. In further detail, 3 sets of CSF pump device parameters may be collected and stored in a default CSF pump device prescription database 526. The default CSF pump device prescription database 526 may be configured to store biometric data (height, sitting height, age, weight, body mass index, health status, etc.) for each user 12. The default CSF pump device prescription database 526 may be configured to store the default position of the CSF pump device 10, which the CSF pump device 10 may be configured to assume when the user 12 enters the CSF pump device 10. Typically, the default position will be both the entry position and the exit position from the device for the user 12. The exit position may be configured to be different from the entry position. The default CSF pump device prescription database 526 stores values for the parameters to configure the CSF pump device 10 in the FTP. The default CSF pump device prescription database 526 stores values for the parameters to configure the CSF pump device 10 in the STP. In addition to the default CSF pump device prescription database 526 being configured to store values for the user 12 at a first treatment session that may be accessed at a later second Z. Grajcar DKT. NO.408439-X treatment session, the default CSF pump device prescription database 526 may be used to provide default values for the user 12 who has never had a treatment session. Control system may be configured to access a data set of multiple user 12 biometric data that may be the same or similar to the biometric data of the new user 12. Only, the default values for entry position, FTP, and STP obtained from the data set of the multiple user 12 biometric data may be used as the default values for the new user 12, or as the starting point for the default values of the new user 12. Each of the database 526s described in the disclosure may be in a plurality of independent database 526s in separate files. Each of the database 526s described in the disclosure may be in a single database 526. Each of the database 526s may be local to the control system, the CSF pump device 10, or in a distributed client / server configuration in a network setting, or any combination thereof. SET UP CSF PUMP AND OTHER STIMULATION DEVICES FOR USE The control system may be configured to determine values for the various parameters that will be used for the stimulation devices to optimize for the user 12 CSF dynamics, CSF flow, and CSF flux; and Glymphatic clearance. Recall, the treatment session comprises one or more treatment cycle. Each treatment cycle in the treatment session may be configured to optimize treatment of the user 12. Therefore, the values for the various parameters that will be used for the stimulation devices used on the user 12 may be configured for each treatment cycle. Each treatment session may be configured to optimize treatment of the user 12. Treatment of the user 12 may change CSF dynamics of the user 12. Treatment of the user 12 may increase CSF volume of the user 12. Treatment of the user 12 may decrease CSF volume of the user 12. Treatment of the user 12 may increase CSF flux of the user 12. Treatment of the user 12 may decrease CSF flux of the user 12. Treatment of the user 12 may increase CSF flow of the user 12. Treatment of the user 12 may decrease CSF flow of the user 12. Values may be needed for the parameters of the various adjustment mechanisms configured to position the CSF pump 100 in a treatment position that fits a user 12 for treatment cycles of a treatment session. Values may be needed for the parameters of the various actuation mechanisms configured for oscillatory movement of the CSF pump 100 between the FTP and the STP during the treatment cycles of the treatment session to change the CSF dynamics of the user 12. The change may be optimization of the CSF dynamics of the user 12. The change may increase of the CSF dynamics of the user 12. The change may be decrease the CSF dynamics of the user 12. Z. Grajcar DKT. NO.408439-X Values may be needed for the parameters of the various actuation mechanisms configured for oscillatory movement of the CSF pump 100 between the FTP and the STP during the treatment cycles of the treatment session to change the CSF flux of the user 12. The change may be optimization of the CSF flux of the user 12. The change may increase the CSF flux of the user 12. The change may decrease of the CSF flux of the user 12. Values may be needed for the parameters of the various actuation mechanisms configured for oscillatory movement of the CSF pump 100 between the FTP and the STP during the treatment cycles of the treatment session to change the CSF flow of the user 12. The change may be optimization of the CSF flow of the user 12. The change may increase the CSF flow of the user 12. The change may decrease of the CSF flow of the user 12. Values may be needed for the parameters of the various actuation mechanisms configured for oscillatory movement of the CSF pump 100 between the FTP and the STP during the treatment cycles of the treatment session to change the Glymphatic clearance of the user 12. The change may be optimization of the Glymphatic clearance of the user 12. The change may be increase of the Glymphatic clearance of the user 12. The change may be decrease of the Glymphatic clearance of the user 12. The values for the one or more of the various parameters may be determined from a database 526. The stimulation database 526 may be configured to record values for treatment parameters for one or more of the stimulation devices used on one or more user 12, and the monitoring database 526 may be configured to record values for activity sensed and recorded for one or more of the monitoring devices used on one or more user 12. Again recall, the CSF dynamics may be affected by cardiac activity, respiration activity, and movement activity of the user 12. Traditionally, respiration activity may be considered to have far greater effect on CSF dynamics than cardiac activity. It may be only recently that the role of movement activity on CSF dynamics has been appreciated. Hence, the Moto-Glymphatic theory. The CSF pump device 10 and other stimulation devices may be configured to change the cardiac activity, the respiration activity, and the movement activity of the user 12. The CSF pump device 10 may be configured to change movement activity of the user 12, and specifically movement activity of the CSF system of the user 12. The CSF pump device 10 produces any arbitrary movement of the CSF system of the user 12. Various breathing activities, such as might be seen in meditation, yoga, etc., may be configured to change respiration activity of the user 12. The CSF pump device 10 may be configured to gait the respiration activity of the user 12. For example, during normal respiration activity, the user 12 undergoes extension of the spinal column during inhalation and flexion of the spinal column during exhalation. The extension of the spinal column during inhalation and Z. Grajcar DKT. NO.408439-X the flexion of the spinal column during exhalation may be subtle and may not even be noticed by the user 12 unless their attention may be drawn to the movements. These movements makes sense from a respiratory biomechanics standpoint. During inhalation, the diaphragm separating the thoracic cavity from the abdominal cavity tightens or shortens and that in turn increases the thoracic cavity volume and therefore the lung volume. The increase in lung volume decreases the pressure in the lungs, therefore there may be an inflow of respiratory gas into the lungs. During exhalation, the diaphragm relaxes or lengthens and returns to its normal dome-shaped and that in turn decreases the thoracic cavity volume and therefore the lung volume. The decrease in lung volume increases the pressure in the lungs, therefore there may be an outflow of respiratory gas out of the lungs. The CSF pump device 10 may be configured to work with respiratory biomechanics to optimize the effect of respiratory activity and movement activity of the CSF on one or more of the CSF dynamics, flow, and flux; and Glymphatic clearance. The CSF pump device 10 may be configured to gait the respiratory activity with inhalation from FTP to STP and exhalation from STP to FTP. At first use of the CSF pump device 10 on the user 12, the CSF pump device 10 may be configured for arbitrary respiratory activity inhalation and exhalation, such as 5 second inhalation followed immediately by 7 second exhalation. At first use of the CSF device on the user 12, the CSF pump device 10 may be configured for respiratory activity inhalation and exhalation based on values of the parameters for the CSF pump device 10 found in the stimulation database 526 for subjects of similar biometrics. After first the use of the CSF pump device 10 on the user 12, the CSF pump device 10 may be configured for respiratory activity inhalation and exhalation based on response to values of the parameters in the monitoring database 526 for the user 12 themselves. Respiration activity may be monitored during set up phase of the CSF device to determine appropriate values used to configure the CSF pump device 10. The CSF pump device 10 and other stimulation device values for the various parameters consider any pre-existing conditions for the user 12. For example, has the user 12 had spinal surgery, spinal degenerative disease, spinal degenerative disc disease, abnormal lumbar lordosis, abnormal thoracic kyphosis, abnormal cervical lordosis, etc. by way of example and not limitation may be obtained by the operator and placed in the database, or the user may do it themselves. Any particular physical condition may or may not be a contraindication to a treatment session. A tilt table research related to orthostatic hypotension may inform CSF pump device values for the various parameters. Supine position may be described as 0°. Standing upright position Z. Grajcar DKT. NO.408439-X may be described as 90°. From tilt table research it may be known that somewhere between 60° and 80° upright most subjects will experience autonomic nervous system sympathetic and parasympathetic responses as if the user 12 may be standing upright. At less than 60° most subjects do not experience autonomic nervous system responses as if the user 12 may be standing upright. This autonomic nervous system response may be based on the baroreceptors found in the aortic arch and at the bifurcation of the internal and external carotid artery. While the hip point to aortic arch angle may not experience significant change during treatment with the CSF pump device 10, there may be motion at the aortic arch experienced by the baroreceptors. And most definitely the carotid bifurcation that in most subjects may be near the jawline will experience change an angle with cervical spine flexion and extension. The autonomic nervous system response to the user 12 standing upright may be too close or at least make it harder to open valves in the internal jugular vein. Closure of the valves in the internal jugular vein would decrease flow of blood towards the heart and decrease Glymphatic clearance from the neck 408 and above, and decrease Glymphatic clearance. Of note, flexion and extension of the neck 408 may massage the lymph nodes near the internal jugular vein, so it may be helpful to keep them open. For this reason, the treatment position disclosed may be considered a zero gravity position or a modified zero gravity position. While the traditional zero gravity position may be considered to have the back of the user 12 on a 30° incline and the thigh of the user 12 on a 30° incline with the knee 416 at approximately the level of the heart, such a position may not be optimum for the CSF pump device 10. An approximately 16° incline of the back and the thigh of the user may be used for a zero gravity position. Any the degrees incline that help the user reached the zero gravity position may be used. Recall the CSF pump device 10 may be configured to have one or more of CSF pump for cervical extension and flexion, thoracic extension and flexion, and lumbar extension and flexion. If the CSF pump device 10 may be placed in a zero gravity position with the back inclined at 30° then there may be only 30° of cervical flexion before the user 12 may experience autonomic nervous system response as if the user 12 may be standing upright. Therefore, the CSF pump device 10 may be configured to have a back angle incline of less than the traditional 30° found in the zero gravity position. The treatment position angle of 16° has been found to create a good balance between placing the user 12 in a comfortable position while increasing the angle of cervical flexion before the upright autonomic nervous system activity occurs. A hydrostatic indifference point for user 12 may be determined and that angle may be used for the treatment position angle. The point inside the static circulatory system where pressure and therefore wall stress remains stable irrespective of the change in position. This point Z. Grajcar DKT. NO.408439-X describes the reference point from which the hydrostatic pressure at the baroreceptors may be determined. When the baroreceptors may be positioned above this point, the hydrostatic contribution to arterial pressure at the level of the baroreceptor may be decreased. Tilt table information may be obtained for the individual user 12 and that information may be used to configure the CSF pump device 10 to optimize cervical flexion and extension angles that can be utilized during the treatment cycle. The tilt table information may be stored in the stimulation database 526 and / or the monitoring database 526. The treatment position angle plus the cervical flexion angle may be less than about 60° to about 80°. The treatment position angle plus the cervical flexion angle may be less than the value defined for the user 12 from tilt table information. The tilt table position angle plus the cervical flexion angle may be less than about 50°, about 51°, about 52°, about 53°, about 54°, about 55°, about 56°, about 57°, about 58°, about 59°, about 60°, about 61°, about 62°, about 63°, about 64°, about 65°, about 66°, about 67°, about 68°, about 69°, about 70°, about 71°, about 72°, about 73°, about 74°, about 75°, about 76°, about 77°, about 78°, about 79°, about 80°, about 81°, about 82°, about 83°, about 84°, about 85°, about 86°, about 87°, about 88°, and about 89°. While some subjects may be able to have the CSF pump device 10 configured to provide the same FTP and STP for each of the one or more CSF pumps throughout the treatment session, the user 12 may have one or more different FTP associated with one or more STP for one or more of the CSF pump 100s 100 in the CSF pump device 10. See FIGS.80-82. The CSF pump device 10 may be configured to provide cervical flexion at a first angle initially during the treatment session and cervical flexion at a second increased angle relative to the first angle as the treatment session progresses. The CSF pump device 10 may be configured to provide cervical flexion at a first angle during the treatment session and cervical flexion at a second decreased angle relative to the first angle as the treatment session progresses. The CSF pump 100 may be configured to provide cervical extension at a first angle during the treatment session and cervical extension at a second increased angle relative to the first angle as the treatment session progresses. The CSF pump 100 may be configured to provide cervical extension at a first angle during the treatment session and cervical extension at a second decreased angle relative to the first angle as the treatment session progresses. The CSF pump 100 may be configured to provide cervical flexion at a first angle initially during the treatment session and cervical flexion at a second increased angle relative to the first angle as the treatment session progresses. The CSF pump 100 may be configured to provide cervical flexion at a first angle during the treatment session and cervical flexion at a second decreased angle relative to the first angle as the treatment session progresses. The CSF pump 100 may be configured to provide cervical extension at a first angle during the treatment session and Z. Grajcar DKT. NO.408439-X cervical extension at a second increased angle relative to the first angle as the treatment session progresses. The CSF pump 100 may be configured to provide cervical extension at a first angle during the treatment session and cervical extension at a second decreased angle relative to the first angle as the treatment session progresses. The CSF pump 100 may be configured to provide lumbar extension at a first span initially during the treatment session and lumbar extension at a second increased span relative to the first span as the treatment session progresses. The CSF pump 100 may be configured to provide lumbar extension at a first span during the treatment session and lumbar extension at a second decreased span relative to the first span as the treatment session progresses. Respiratory activity may be obtained during set up in the control system may be configured to use the respiratory activity obtained during set up to provide values for the various parameters of the CSF pump device 10. This respiratory activity obtained during set up through monitoring may be recorded in the stimulation and / or monitoring database 526. While traditionally, cardiac activity might not be considered to have a great effect on the CSF dynamics, the blood vessels system and therefore the cardiac system may be involved in the CSF dynamics, flow, flux; and Glymphatic clearance. Heart rate variability may be obtained through a cardiac activity monitored during set up. Heart rate variability may be assessed during set up. Heart rate variability information may be used by the control system to configure the treatment cycle in the treatment session of the user 12. The heart rate variability data may be stored in the stimulation and / or monitoring database 526. Brain wave activity may be monitored by electroencephalogram during set up. The user 12 may be provided various visual stimulation, auditory stimulation, and the tactile stimulation during set up and the responses obtained on electroencephalogram. The user 12 may be provided stimulation to induce slow brain wave activity (7 Hz or less), alpha brain wave activity, or beta of brain wave activity or any combination of the same, which can be monitored by EEG. HEART RATE VARIABILITY Any of the devices and methods disclosed elsewhere in this disclosure may be used in conjunction with the following disclosures regarding heart rate variability. The following information serves as a reminder of details disclosed elsewhere in this application. While our understanding of cerebrospinal fluid (CSF) dynamics is continually evolving, several physical and biomechanical principles and procedures have been scientifically established that affect CSF movement. Z. Grajcar DKT. NO.408439-X At rest, CSF is primarily produced in the choroid plexus within the brain’s ventricles and is absorbed into the bloodstream in the arachnoid villi. With movement of the CSF system, CSF is produced in other areas, such as the lumbar cistern that allows inflow of interstitial fluid that becomes CSF in the subarachnoid space. The balance between CSF production and absorption is crucial for maintaining a stable CSF volume and pressure. The movement of CSF is influenced by fluid dynamics principles, such as Bernoulli’s Principle, which describes the relationship between fluid pressure and fluid velocity. Bernoulli’s Principle states that an increase in the speed of a parcel of fluid (liquid or gas) occurs simultaneously with a decrease in either the pressure or the height above a reference point. Changes in pressure gradients and flow rates impact CSF circulation. CSF dynamics may be based on pulsations of the heartbeat and / or the respiration and / or low frequency vasomotor waves (Mayer & Traube-Hering waves). The rhythmic heartbeat creates CSF pulsation. During systole (the heart’s contraction phase), CSF in perivascular spaces is displaced by dilating vasculature, while during diastole (the heart’s relaxation phase), CSF is drawn back into perivascular spaces. Body posture, physical activity, and changes in body position can also influence CSF circulation. For example, an upright posture and physical activity may facilitate CSF movement, potentially more than changes in heart rate alone. The respiratory cycle regulates CSF movement. Respiration creates a pulsation or rhythmic fluctuation in CSF flow. This pulsation is due to the cyclical changes in thoracic pressure that occur during breathing. Specifically, during inspiration, the expansion of the chest cavity 404 lowers intrathoracic pressure. This draws more venous blood into the thorax, increasing blood volume and pressure in the thoracic vasculature. The increased pressure is then transmitted to the CSF space, causing a brief rise in CSF pressure with each inhalation. The cyclical fluctuations in CSF pressure due to respiration create a pulsation or rhythmic pumping of CSF within the CSF system of the brain and spinal cord. Studies have consistently found that forced inspiration is associated with an upward CSF movement in the entire spinal canal, causing unidirectional CSF flow in the brain. Mayer & Traube-Hering (MTH) waves are cyclic changes or waves in arterial blood pressure brought about by oscillations in the baroreceptor reflex control system. The MTH waves are seen both in the electrocardiography / photoplethysmography records and in continuous blood pressure curves. MTH waves can be defined as arterial blood pressure oscillations at frequencies slower than respiratory frequency and that show the strong coherence with efferent sympathetic nervous activity. The hemodynamic basis of MTH waves are oscillations of the sympathetic vasomotor Z. Grajcar DKT. NO.408439-X tone of arterial blood vessels, because MTH waves are strongly attenuated by pharmacological blockade of alpha-adrenoreceptors. Within a given biological species, their frequency is fairly stable and in humans does not depend on gender, age, or posture. In humans, the oscillations which meet these properties have a characteristic frequency of about 0.1 Hz. MTH waves are correlated with heart rate variability. According to the Moto-Glymphatic Theory, the cerebrospinal fluid clearance can be increased through increased pressure and changes of pressure in the CSF system. While traditionally, cardiac activity is not considered to have a great effect on the CSF dynamics, the blood vessels system and therefore the cardiac system are involved in the CSF dynamics, flow, flux, and glymphatic clearance. Optionally, heart rate variability is obtained through a cardiac activity monitored during set up. Optionally, heart rate variability is assessed during set up. Optionally, heart rate variability information is used by the control system to configure the treatment cycle in the treatment session of the subject. Optionally, the heart rate variability data is stored in the stimulation and / or monitoring database 526. Heart rate (HR) is measured as the number of heartbeats per minute. Heart rate variability (HRV) is the fluctuation in the time interval between consecutive heartbeats. HRV is produced by heart-brain interactions and the autonomic nervous system (ANS). A healthy heart in a subject has beat-to-beat complex fluctuations that can be described by chaos theory. An optimal level of HRV is associated with health, while disease has a loss or increase of the complexity. In the scientific and medical literature, HRV is typically described over 24 hours, short-term (ST, ~5 minutes) or brief, and ultra-short-term (UST, <5 minutes) using time-domain, frequency- domain, and non-linear measurements. Electrocardiography (ECG) or photoplethysmography (PPG) can measure the heart rate used to calculate HRV. ECG is considered the gold standard for measuring heart activity, but it requires electrode placement close to the heart of the subject. PPG indirectly measures heart rate and can be measured anywhere on the subject with adequate access to skin vessels, so PPG can be more convenient. PPG data can be obtained from a variety devices. For example, a Garmin Vivoactive Smartwatch (Garmin Ltd., Olathe, KS) can be used for PPG measurements. Time-domain indices of HRV quantify the amount of variability in measurements of the interbeat interval (IBI), which is the time period between successive heartbeats. IBI is generally measured in milliseconds. Frequency-domain measurements estimate the distribution of absolute or relative power into four frequency bands. Power is the signal energy found within a frequency band. Z. Grajcar DKT. NO.408439-X The ULF band (≤0.003 Hz) measures fluctuations in IBI with a period from 5 minutes to 24 hours and is measured using 24 hours recordings, so it will not be discussed further in the present disclosure. For further details on HRV, please see An Overview of Heart Rate Variability Metrics and Norms by Shaffer, Fred and Ginsberg, J. P., Front. Public Health, 27 September 2017, Sec. Family Medicine and Primary Care, Volume 5 - 2017, https: / / doi.org / 10.3389 / fpubh.2017.00258, which is incorporated by reference herein. The VLF band (0.0033–0.04 Hz) is typically comprised of rhythms with periods between 25 seconds and 300 seconds. However, the frequency band may be adjusted, as needed, to meet the particular needs of the heart rate characteristics being measured. The LF band (0.04–0.15 Hz) is comprised of rhythms with periods between 7 seconds and 25 seconds and is affected by breathing from ~3 to 9 bpm. Within a 5 minutes sample, there are 12- 45 complete periods of oscillation. Again, the frequency band may be adjusted, as needed, to meet the particular needs of the heart rate characteristics being measured. The HF, or respiratory, band (0.15–0.40 Hz) is influenced by breathing from 9 to 24 bpm. Two distinct but overlapping processes generate short-term HRV measurements. The first source is a relationship between parasympathetic nervous system (PNS) and sympathetic nervous system (SNS). The second source includes the regulatory mechanisms that control HR via respiratory sinus arrhythmia (RSA), the baroreceptor reflex (negative-feedback control of blood pressure (BP)), and rhythmic changes in vascular tone. RSA refers to the respiration-driven speeding and slowing of the heart via the vagus nerve. In a healthy human heart, there is a complex dynamic relationship between PNS and SNS. PNS exerts its effect more rapidly (<1 second) than SNS (>5 seconds) and should not be described as a “zero sum” system. Baroreceptors, which are BP sensors located in the aortic arch and internal carotid arteries, contribute to short-term HRV. When a subject inhales, HR increases and BP rises about 4-5 s later. Baroreceptors detect the BP rise and fire more rapidly. When a subject exhales, HR decreases, and BP falls about 4-5 seconds later. The baroreflex makes possible this acceleration and deceleration of the heart, called RSA. The baroreflex links HR, BP, and vascular tone of blood vessels. Baroreceptor firing due to BP changes activates mechanisms that change HR and vascular tone. Rising BP triggers decreases in HR and vascular tone, while falling BP causes increases HR and vascular tone. One can use Fast Fourier Transformation (FFT) or other techniques to separate HRV signal into its component ULF, VLF, LF, and HF rhythms that operate within different frequency ranges. Z. Grajcar DKT. NO.408439-X The VLF band (0.0033–0.04 Hz) requires a recording period of at least 5 minutes. Very-low- frequency power may also be generated by physical activity, thermoregulatory, renin– angiotensin, and endothelial influences on the heart. PNS may contribute to VLF power because SNS blockade almost completely abolishes it. The LF band (0.04–0.15 Hz) is typically recorded over a minimum 2 min period. LF power may be produced by both PNS and SNS, and BP regulation via baroreceptors, primarily by the PNS or by baroreflex activity alone. SNS does not appear to produce rhythms much above 0.1 Hz, while the parasympathetic system can be observed to affect heart rhythms down to 0.05 Hz. In resting conditions, the LF band reflects baroreflex activity. During periods of slow respiration rates, vagus nerve activity can generate oscillations in the heart rhythms that are in the LF band. Therefore, respiratory-related efferent vagally mediated influences are particularly present in the LF band when respiration rates are below 8.5 bpm (each breath takes ~ 7 seconds). The HF, which is sometimes called the respiratory, band (0.15–0.40 Hz) is conventionally recorded over a minimum 1 min period. The HF band reflects PNS and is called the respiratory band because HF band corresponds to the HR variations related to the respiratory cycle. These phasic HR changes are known as RSA and may not be a pure index of cardiac vagal control. Heart rate accelerates during inspiration and slows during expiration. During inhalation, the cardiovascular center inhibits vagal outflow resulting in speeding the HR. Conversely, during exhalation, it restores vagal outflow resulting in slowing the HR via the release of acetylcholine. In healthy individuals, RSA can be increased by slow, deep breathing. Larger respiration tidal volumes and lower respiration rates increase RSA. Increasing or decreasing respiration rate from a client’s resonance frequency, the breathing rate that best stimulates the cardiovascular system, may lower short-term time-domain measurements and LF band power, while raising or lowering HF power, respectively. Short-term measurement norms are based on ~5 minutes of HRV data. Because of their relative ease of recording, short-term measurements have been widely used and studied for many years, and appear to be the most commonly found source of published HRV data. Short-term values are only appropriate when clients breathe at normal rates (~11–20 bpm). The normal respiratory rate for healthy adults is between 12–20 breaths per minute. The central premise of the HRV biofeedback resonance frequency model is that the adult cardiorespiratory system has a fixed resonance frequency. Stimulation at rates near the resonance frequency produces large-amplitude blood pressure oscillations that can increase baroreflex sensitivity over time. During resonance frequency biofeedback, the only relevant metrics are LF Z. Grajcar DKT. NO.408439-X ms2 or peak frequency since breathing from 4.5 to 7.5 bpm concentrates HR oscillations around 0.1 Hz in the LF band. ANS and circulating hormones modulate SA node initiation of heartbeats. The interdependent regulatory systems that generate the complex variability of a healthy heart operate over different time scales to achieve homeostasis and optimal performance. The complex dynamic relationship between the PNS and SNS, and homeostatic regulation of HR via respiration and the baroreceptor reflex are responsible for short-term and ultra-short-term HRV measurements. Short-term measurement norms can contribute to assessment before, during, and after HRV biofeedback training for both clinical and optimal performance. The central premise of the HRV biofeedback resonance frequency model is that the adult cardiorespiratory system has a fixed resonance frequency. Stimulation at rates near the resonance frequency produces large-amplitude blood pressure oscillations that can increase baroreflex sensitivity over time. See A Practical Guide to Resonance Frequency Assessment for Heart Rate Variability Biofeedback, Shaffer, Fred and Meehan, Zachary M., Front. Neurosci., 07 October 2020, Sec. Autonomic Neuroscience, Volume 14 - 2020, https: / / doi.org / 10.3389 / fnins.2020.570400 and correction Corrigendum: A Practical Guide to Resonance Frequency Assessment for Heart Rate Variability Biofeedback, Shaffer, Fred and Meehan, Zachary M., Front. Neurosci., 30 November 2020, Sec. Autonomic Neuroscience, Volume 14 - 2020, https: / / doi.org / 10.3389 / fnins.2020.627512, which is incorporated by reference herein for further details. Determination of the resonance frequency is a prerequisite for HRV biofeedback resonance frequency training because adult peak frequencies range between 0.075 and 0.11 Hz. The analysis can be conducted in the very low frequency or VLF (0.008–0.1 Hz), respiratory (0.1–0.6 Hz), and cardiac (0.6–5 Hz) bands. We may analyze these coupling relationships in the original sampling and downsampling frequencies, 800 Hz and 10 Hz, respectively. Downsampling from 800 to 10 Hz may enable a more comprehensive analysis with Magnetic Resonance Encephalography (MREG) data in the future. A sliding window with pre-defined width for each band is set. The window width is determined based on the maximum wavelength of the targeted physiological signal source in the selected bands; in the VLF vasomotor band the window is set to 120 s, in the respiratory band for 10 s, and 2 s for the cardiac band. We can extend this width up to 1.5 times the starting width with two values in between to get four window width values for each band. For example, the window width parameters in the VLF band may be 120 s, 140 s, 160 s, and 180 s. Using a larger window, we may be able to analyze signal more than one period of oscillation. We may use 25%, 50%, and 75% overlap when the window Z. Grajcar DKT. NO.408439-X See Ferdinando, H., Moradi, S., Korhonen, V. et al. Altered cerebrovascular-CSF coupling in Alzheimer’s Disease measured by functional near-infrared spectroscopy. Sci Rep 13, 22364. ACCELERATION AND DECELERATION With an understanding of the cerebrospinal fluid pump device that includes one or more cerebrospinal fluid pump, it is time to address details of how the cerebrospinal fluid pump might operate. FIG.69 shows a graphical representation of position versus time for operation of the cerebrospinal fluid pump in an idealized situation. Two treatment cycles 500 are shown for discussion purposes, although it will be understood that the treatment session may include one or more treatment cycles. In addition, the apparatus and methods disclosed regarding how the cerebrospinal fluid pump might operate cover situations where there may be variability of the timing for flexion, timing for extension, distance for flexion, and distance for extension, for simplicity’s sake in understanding, timing for flexion, timing for extension, distance for flexion, and distance for extension will be kept constant for the purposes of discussion only. The general principles to be disclosed apply to any situation in which there may be variation of the timing for flexion, timing for extension, distance for flexion, and distance for extension. Distance may refer to a linear distance or angular distance or any combination thereof or any other method for measuring length between the first treatment position 502 and the second treatment position 504, which may be characterized as any FTP and STP disclosed herein. The CSF pump 100 may be a thoracolumbar pump configured to change position or move a thoracolumbar spine of the subject. The CSF pump 100 may be a lumbar pump configured to change position or move a lumbar spine of the subject. The CSF pump 100 may be a cervical pump configured to change position or move a cervical spine of the subject. The cerebrospinal fluid pump may oscillate between the first treatment position 502 and the second treatment position 504. The cerebrospinal fluid pump may be configured to move a distance from the first treatment position 502 to the second treatment position 504 in a first prescribed time 506. Movement between the first treatment position 502 and the second treatment position 504 may be at a first steady rate defined as the distance divided by the first prescribed time 506. Movement between the second treatment position 504 and the first treatment position 502 may be configured to move a distance from the second treatment position 504 to the first treatment position 502 in a second prescribed time 508. Movement between the second treatment position 504 and the first treatment position 502 may be at a second steady rate defined as the distance divided by the second prescribed time 508. Z. Grajcar DKT. NO.408439-X In the idealized situation, the environment in which the cerebrospinal fluid pump is operating does not change throughout its operation. For example, the load being displaced by the cerebrospinal fluid pump is constant and does not change throughout movement or operation of the cerebrospinal fluid pump. Such an idealized situation is unlikely to be present due to movement of the subject supported by the cerebrospinal fluid pump device moving relative to the cerebrospinal fluid pump device. The idealized situation is unlikely to be present due to a change of an angle of the cerebrospinal fluid pump device relative to the horizontal support device for the cerebrospinal fluid pump device, also. Anyone skilled in the art can come up with other situations in which the idealized situation may not exist. However, the operation of the cerebrospinal fluid pump as shown in FIG.69 would certainly seem to be a logical manner of operation. Vertical axis 510 shows distance quantity. Horizontal axis 512 shows time with increasing time to the right. Position of the cerebrospinal fluid pump varies during operation and is shown at any given time on a waveform 516 in a sawtooth pattern. There may be a problem using such a manner of operation for the cerebrospinal fluid pump, which becomes apparent when digging further into the details. A negative slope 514 of the waveform 516 corresponds to change in position of the cerebrospinal fluid pump from the first treatment position 502 to the second treatment position 504. A positive slope 518 of the waveform corresponds to change in position of the cerebrospinal fluid pump from the second treatment position 504 to the first treatment position 502. The slope of the waveform 516, also known herein as the curve, at any instance in time is the rate of change of the position relative to the time, otherwise known as velocity. The waveform 516 looks continuous with oscillation between the first treatment position 502 and the second treatment position 504 so one would think the movement experienced by the subject would be smooth and continuous, but what is really happening? In addition to movement from the first treatment position 502 to the second treatment position 504, there is a first transition 520 from movement towards the second treatment position 504 to movement towards the first treatment position 502, and a second transition 522 from movement towards the first treatment position 502 to movement towards the second treatment position 504. Let’s assume the cerebrospinal fluid pump is a cervical pump. The first treatment position 502 may be configured for flexion of the cervical spine and the second treatment position 504 is configured for extension of the cervical spine. Movement of the cerebrospinal fluid pump from the first treatment position 502 to the second treatment position 504 may be configured to create extension of the cervical spine of the subject. Movement of the cerebrospinal fluid pump from the second treatment position 504 to the first treatment position 502 may be configured to create flexion of the cervical spine of the subject. Z. Grajcar DKT. NO.408439-X FIG.70 shows a graphical representation of velocity versus time for operation of the cerebrospinal fluid pump in the idealized situation. FIG.69 and FIG.70 show the same operation of the cerebrospinal fluid pump on the same time scale. However, the vertical axis 510 for FIG. 69 shows distance while the vertical axis 530 for FIG.70 shows distance versus time, otherwise known as velocity. Arguably, FIG. and 69 hides in plain sight the significance of the first transition 520 in movement towards the second treatment position 504 to movement towards the first treatment position 502, and the second transition 522 from movement towards the first treatment position 502 to movement towards the second treatment position 504. The abrupt change from the first steady rate during the first prescribed time 506 towards the second treatment position 504 to the second steady rate during the second prescribed time 508 towards the first treatment position 502 becomes more obvious to one skilled in the art in FIG.70. However, the abrupt change at the first transition 520 and the second transition 522 may be obvious to the subject. With the abrupt transition at the first transition 520 from extension of the cerebrospinal fluid pump during the first prescribed time 506 to flexion of the cerebrospinal fluid pump during the second prescribed time 508, there may be a tendency for the head of the subject to continue extending while the cerebrospinal fluid pump or more generally the cerebrospinal fluid pump device “taps” the head of the subject as the cerebrospinal fluid pump transitions from extension movement to flexion movement. On the other hand, with the abrupt transition a the second transition 522 from flexion of the cerebrospinal fluid pump during the second prescribed time 508 to extension of the cerebrospinal fluid pump during the first prescribed time 506, there may be a tendency for the head of the subject to continue flexing while the cerebrospinal fluid pump transitions from flexion movement to extension movement such that there is separation of the head of the subject from the cerebrospinal fluid pump and more generally the cerebrospinal fluid pump device. The head of the subject may ultimately flop back towards the cerebrospinal fluid pump and more generally the cerebrospinal fluid pump device and experience a “tap” of the head of the subject from the cerebrospinal fluid pump or more generally the cerebrospinal fluid pump device or the subject may ultimately flop forwards away from the cerebrospinal fluid pump and more generally the cerebrospinal fluid pump device, such that the cerebrospinal fluid pump movement from the first treatment position 502 to the second treatment position 504 no longer is configured to affect movement of the subject and so no longer is configured to affect the cerebrospinal fluid dynamics of the subject. Slope 514 in the distance versus time graph of FIG. and was 69 corresponds to the negative velocity 514 in the velocity versus time graph of FIG.70. The area 532 under the curve during the first prescribed time 506 may equal the area 534 under the curve during the second prescribed treatment time, as shown. Z. Grajcar DKT. NO.408439-X Nature may provide a clue how to deal with the abrupt transition. FIG.71 shows a graphical representation in the subject of airflow over time to the right. This airflow over time is analogous to change in distance over time, a.k.a. velocity Two cycles of respirations are shown, although of course the general idea discussed applies to one or more cycles of respiration. For simplicity, the idealized respiration pattern shown has equal inhalation and exhalation times. The same general discussion would apply for situations in which the inhalation time is less than exhalation time, or vice versa. Inhalation volume under the curve during inhalation needs to be approximately the same as exhalation volume under the curve during exhalation. If inhalation volume exceeds exhalation volume, then there will be a build-up or increase of air volume in the subject. If exhalation volume exceeds inhalation volume, then there will be restriction or decrease of air volume in the subject. Respiration involves lungs and supporting structures that can be characterized as viscoelastic elements in modeling. For our purposes, the insight is there is an acceleration of airflow followed by deceleration of airflow in a repeating pattern for each inhalation and exhalation. FIG.72 shows a graphical representation of operation of the cerebrospinal fluid pump with acceleration and deceleration of movement of the cerebrospinal fluid pump. Inhale time is prescribed as the first prescribed time 506, also known herein as the prescribed inhalation time 506. Distance to be covered during the inhale time is prescribed. The motor is configured to move the cerebrospinal fluid pump. The velocity curve or waveform 550 for movement of the cerebrospinal fluid pump may be a sinusoidal curve during the inhalation time. The slope 552 of the velocity waveform 550 at any instance in time is defined as acceleration. The movement of the cerebrospinal fluid pump shown in FIG.72 may produce better biomimicry of movements of the subject and associated respiration pattern of the subject, however, other waveforms are contemplated. The motor may move faster to provide acceleration of the cerebrospinal fluid pump. The motor may move slower to provide deceleration of the cerebrospinal fluid pump. The peak 554 of the velocity waveform 550 may be at about the midpoint or about 50% of the prescribed inhalation time 506. The optional sinusoidal shape of the velocity waveform 550 may be implemented through an algorithm such as a predetermined template that accounts for distance of the cerebrospinal fluid pump to be moved during the prescribed inhalation time 506. The algorithm for movement of the cerebrospinal fluid pump may be implemented as a table look up for velocity of the cerebrospinal fluid pump at different times in the position of the cerebrospinal fluid pump during the prescribed inhalation time 506. The algorithm for movement of the cerebrospinal fluid pump Z. Grajcar DKT. NO.408439-X may be implemented as a table look up for acceleration of the cerebrospinal fluid pump at different times in the velocity of the cerebrospinal fluid pump during the prescribed inhalation time 506. The algorithm for movement of the cerebrospinal fluid pump may be implemented as a mathematical formula for velocity of the cerebrospinal fluid pump at different times in the position of the cerebrospinal fluid pump during the prescribed inhalation time 506. The algorithm for movement of the cerebrospinal fluid pump may be implemented as a mathematical formula for acceleration of the cerebrospinal fluid pump at different times in the velocity of the cerebrospinal fluid pump during the prescribed inhalation time 506. Whatever the algorithm, the cerebrospinal fluid pump may be configured to move the distance from the first treatment position to the second treatment position with acceleration to a first movement velocity greater than a steady state 560 defined as the distance divided by the first prescribed (or prescribed inhalation) time and deceleration to a second movement velocity less than the steady state. The algorithm would need to account for area under the curve for the velocity of the cerebrospinal fluid pump v. time, such that the total amount of distance moved during the prescribed inhalation time achieves the prescribed target for movement during the prescribed inhalation time. A stepper motor may be used to implement the acceleration and deceleration of the cerebrospinal fluid pump movement may have certain limitations. For a stepper motor to accurately accelerate or decelerate the cerebrospinal fluid pump to an exact velocity or distance at an exact time could be a big decimal number that is not practical to use for control of the stepper motor. A motor driver for the stepper motor may only have so much accuracy so it may be useful to adjust and offset slope so there is an optional need to recalculate positioning the cerebrospinal fluid pump back to the waveform defined by the algorithm. In simple terms, the cerebrospinal fluid pump needs to go a certain distance in a certain time during the prescribed inhalation time. The stepper motor may have an encoder so that the stepper motor knows where the stepper motor is at any given time. The stepper motor may use this encoder to know where the stepper motor is for every step. The stepper motor, the motor driver, and the controller may be configured to control position, velocity, and acceleration of the cerebrospinal fluid pump during the prescribed inhalation time 506. Exhale time may be prescribed as the second prescribed time 508, also known herein as the prescribed exhalation time 508. Distance to be covered during the exhale time is prescribed. Again, the motor is configured to move the cerebrospinal fluid pump. The velocity curve or waveform 562 for movement of the cerebrospinal fluid pump may be a leaky integrator curve during the exhalation time. The slope 564 of the velocity waveform 562 at any instance in time is defined as acceleration. Other waveforms are contemplated, however, the movement of the Z. Grajcar DKT. NO.408439-X cerebrospinal fluid pump shown in FIG.72 may produce better biomimicry of movements of the subject and associated respiration pattern of the subject, as previously noted. The motor may move faster to provide acceleration of the cerebrospinal fluid pump. The motor may move slower to provide deceleration of the cerebrospinal fluid pump. The peak 566 of the velocity waveform 562 may be at about one third or about 33% of the prescribed exhalation time 508. The leaky integrator shape of the velocity waveform 562 may be implemented through an algorithm such as a predetermined template that accounts for distance of the cerebrospinal fluid pump to be moved during the prescribed exhalation time. The algorithm for movement of the cerebrospinal fluid pump may be implemented as a table look up for velocity of the cerebrospinal fluid pump at different times in the position of the cerebrospinal fluid pump during the prescribed exhalation time 508. The algorithm for movement of the cerebrospinal fluid pump may be implemented as a table look up for acceleration of the cerebrospinal fluid pump at different times in the velocity of the cerebrospinal fluid pump during the prescribed exhalation time 508. The algorithm for movement of the cerebrospinal fluid pump may be implemented as a mathematical formula for velocity of the cerebrospinal fluid pump at different times in the position of the cerebrospinal fluid pump during the prescribed exhalation time 508. The algorithm for movement of the cerebrospinal fluid pump may be implemented as a mathematical formula for acceleration of the cerebrospinal fluid pump at different times in the velocity of the cerebrospinal fluid pump during the prescribed exhalation time 508. Whatever the algorithm, the cerebrospinal fluid pump may be configured to move the distance from the second treatment position to the first treatment position with acceleration to a first movement velocity greater than a steady state defined as the distance divided by the second prescribed (or prescribed exhalation) time and deceleration to a second movement velocity less than the steady state. The algorithm may be configured to account for area under the curve for the velocity of the cerebrospinal fluid pump v. time, such that the total amount of distance moved during the prescribed exhalation time achieves the prescribed target for movement during the prescribed exhalation time. A stepper motor used to implement the acceleration and deceleration of the cerebrospinal fluid pump movement may have certain limitations, as discussed previously. For a stepper motor to accurately accelerate or decelerate the cerebrospinal fluid pump to an exact velocity or distance at an exact time could be a big decimal number that is not practical to use for control of the stepper motor. A motor driver for the stepper motor may only have so much accuracy so it may be useful to adjust and offset slope so there is an optional need to recalculate positioning the cerebrospinal fluid pump back to the waveform defined by the algorithm. In simple terms, the cerebrospinal fluid pump needs to go a certain distance in a certain time during the prescribed Z. Grajcar DKT. NO.408439-X exhalation time. The stepper motor may have an encoder so that the stepper motor knows where the stepper motor is at any given time. The stepper motor can use this encoder to know where the stepper motor is for every step. The stepper motor, the motor driver, and the controller is configured to control position, velocity, and acceleration of the cerebrospinal fluid pump during the prescribed exhalation time. Acceleration portion 570 of waveform 550 is shown in more detail in FIG.73. Deceleration portion 580 of waveform 562 is shown in more detail in FIG.74. FIG.73 shows in detail error correction during operation of the cerebrospinal fluid pump with acceleration and deceleration of movement of the cerebrospinal fluid pump. Waveform 550 has one or more checkpoints. Going from top to bottom of the figure, one sees a total of 5 checkpoints on the waveform 550, but there may be one or more checkpoint. Time is measured as increasing from left to right in the figure. At the first checkpoint 571, the first position 581 of the waveform 550 is measured along a timeline 579. The first position 581 of the waveform 550 is within the first checkpoint 571 so no adjustment is needed. At the second checkpoint 572, the second position 582 of the waveform 550 is to the left 577 of the second checkpoint 572. That means on the velocity v. time curve that the second position 582 is reached before the time intended. Therefore, an adjustment needs to be made. In other words, the velocity of the cerebrospinal fluid pump needs to be slowed during acceleration. At the third checkpoint 573, the third position 583 of the waveform 550 is within target of the third checkpoint 574. That means on the velocity v. time curve that the third position is reached within tolerance of the checkpoint measurement system. No adjustment needs to be made. At the fourth checkpoint 574, the fourth position 584 of the waveform 550 is to the right 578 of the fourth checkpoint 574. That means on the velocity v. time curve that the fourth position 584 is reached after the time intended. Therefore, an adjustment needs to be made. In other words, the velocity of the cerebrospinal fluid pump needs to be increased during acceleration. At the fifth checkpoint 575, the fourth position 585 is within the fifth checkpoint 575 so no adjustment is needed. FIG.74 shows a graphical representation of operation of the cerebrospinal fluid pump with acceleration and deceleration of movement of the cerebrospinal fluid pump with a sawtooth waveform for the velocity curve. Waveform 562 has one or more checkpoints. Going from top to bottom of the figure, one sees a total of 6 checkpoints on the waveform 562, but there may be one or more checkpoints. Time is measured as increasing from left to right in the figure. At the first checkpoint 591, the first position 601 of the waveform 562 is measured along a timeline 599. The first position 591 of the waveform 562 is within the first checkpoint 591 so no adjustment is needed. At the second checkpoint 592, the second position 602 of the waveform Z. Grajcar DKT. NO.408439-X 562 is within the second checkpoint 592 so no adjustment is needed. At the third checkpoint 593, the third position 603 to the left 597 of the third checkpoint 593. That means on the velocity v. time curve that the second position 582 is reached before the time intended. Therefore, an adjustment needs to be made. In other words, the velocity of the cerebrospinal fluid pump needs to be increased during deceleration. At the fourth checkpoint 594, the fourth position 604 of the waveform 562 is within target of the fourth checkpoint 594. That means on the velocity v. time curve that the third position is reached within tolerance of the checkpoint measurement system. No adjustment needs to be made. At the fifth checkpoint 595, the fifth position 605 of the waveform 562 is to the right 598 of the fifth checkpoint 595. That means on the velocity v. time curve that the fifth position 605 is reached after the time intended. Therefore, an adjustment needs to be made. In other words, the velocity of the cerebrospinal fluid pump needs to be slowed during deceleration. At the sixth checkpoint 596, the sixth position 606 is within the sixth checkpoint 596 so no adjustment is needed. The slope connecting each of the error correction checkpoints with the next error correction checkpoint may be a straight line. The slope connecting each of the error correction checkpoints with the next error correction checkpoint may be curvilinear. As a reminder, when the velocity v. time waveform is used, the slope at any given time corresponds to acceleration and when distant or position v. time is used, the slope at any given time corresponds to velocity. This acceleration and deceleration control mechanism may create an opportunity to have setting parameters with maximum velocity of the CSF pump between the 1st treatment position and the 2nd treatment position and between the 2nd treatment position in the 1st treatment position with error correction to adjust trajectory of the oscillation movement. The driving factor of the movement may be acceleration and deceleration of the CSF pump as it oscillates. METHODS FOR CONTROL OF THE CSF PUMP DEVICE 10S, AND STIMULATING AND MONITORING OF THE USER With an understanding of the control systems for the CSF pump device 10s and the stimulating and monitoring of the user 12, methods configured for optimizing glymphatic clearance of the central nervous system, and changing the CSF volume in the CSF system may be disclosed. FIG.75 shows a method for using the CSF pump device 10 to treat the user 12 during a treatment session. It may be understood that each step may be optional in the method of using the CSF pump device 10 to treat the user 12 during the treatment session comprises more or less steps. At START 300, start the method of using CSF pump device. Z. Grajcar DKT. NO.408439-X At FIRST STEP 302, obtain the CSF pump device 10 configured to pump the CSF in the CSF system of the user 12. At SECOND STEP 404, use the control system to configure the values of the parameters of the CSF pump device 10 in the entry position for the user 12 to enter the CSF pump device 10. The values of the parameters of the CSF pump device 10 in the entry position for the user 12 may be revised from the default values used to configure the values of the parameters of the CSF pump device 10 in the entry position. The revision makes entry of the user 12 into the CSF pump device 10 easier at a later treatment session. The values of the parameters of the CSF pump device 10 in the entry position for the user 12 may be stored in the default CSF pump device prescription database 526. The values of the parameters of the CSF pump device 10 in the entry position may be used during a later treatment session. At THIRD STEP 406, position the CSF pump device 10 adjacent to the user 12 so that the CSF pump device 10 may be configured to pump the CSF in the CSF system in the user 12. The control system may be configured to move the one or more CSF pumps of the CSF pump device 10 in relation to the user 12 and each other so that the CSF pump device 10 may be configured to pump the CSF in the CSF system in the user 12. At FOURTH STEP 408, determine the FTP and the STP for each of the one or more CSF pumps in the CSF pump device 10. The FTP and the STP for each of the one or more CSF pumps may be determined in any order. The FTP of the one or more of the CSF pump 100s most adjacent to the lumbar spine may be determined first, the FTP of the one or more CSF pumps most adjacent to the cervical spine may be determined second, the STP of the one or more CSF pumps most adjacent to the cervical spine may be determined third, and the STP of the one or more CSF pumps most adjacent to the lumbar spine may be determined last. The FTP and the STP for each of the one or more CSF pumps may be determined by the operator operating the control system and interacting with the user 12. The operator operates the control system to position the one or more CSF pumps in the FTP and the STP. In the FTP of the one or more CSF pumps most adjacent to the lumbar spine, the CSF pump 100 may be configured to be contactingly adjacent the clothing, safety devices, or skin of the user 12 without applying significant force to the user 12. In the STP of the one or more CSF pumps most adjacent to the lumbar spine, the CSF pump 100 may be configured to extend the spine by the one or more of the CSF pump 100s extending anteriorly to apply force to the lumbar spine of the user 12. In the FTP of the one or more CSF pumps most adjacent to the cervical spine, the CSF pump 100 may be configured to place the cervical spine of the user 12 in flexion.. In the STP of the one or more CSF pumps most adjacent to the cervical spine, the CSF pump 100 may be configured to place the cervical spine of the user 12 in extension. Z. Grajcar DKT. NO.408439-X The FTP and the STP for each of the one or more CSF pumps may be determined automatically or semi-automatically by operating the control system. The FTP of the one or more CSF pumps most adjacent to the lumbar spine may be configured to be automatically determined by when force may be sensed by the force transducer coupled to the CSF pump 100 most adjacent to lumbar spine. The force may be sensed when the CSF pump 100 applies force to the user 12. This position may be treated as the FTP. The CSF pump 100 may be retracted posteriorly away from the body of the user 12 to the first retracted position where force may be not sensed by the force transducer coupled to the CSF pump 100 in this first retracted position may be treated as the FTP. The STP of the one or more CSF pumps most adjacent to the lumbar spine may be configured to be semi-automatically determined by when the user 12 presses a selection button for the STP or extension of the CSF pump 100 reaches the maximum CSF pump device position, which may be defined as a span of 1 cm, 2 cm, 3 cm, 4 cm, 5 cm, or more from the FTP to the STP. The user 12 may be trained to press the selection button according to the criteria used in determining the STP of the CSF pump 100 most adjacent to the lumbar spine when the operator may be operating the control system. The FTP of the one or more CSF pumps most adjacent to the cervical spine may be configured to be automatically determined by when force may be sensed by the force transducer coupled to the CSF pump 100 most adjacent to the cervical spine to be at or above some arbitrary force. For example, the head 402 of the user 12 resting on the headrest applies force to the headrest that may be sensed by the force transducer coupled to the CSF pump 100 adjacent to the cervical spine when the cervical spine may be in a neutral anatomic position. As the CSF pump 100 moves the cervical spine into flexion, the force transducer will eventually experience increased force when the cervical spine stops easily moving into flexion. This increased force may be at or above some arbitrary force that may be used to define the FTP of the one or more CSF pumps most adjacent to the cervical spine. If the force at or above some arbitrary force may be not reached but the maximum CSF pump device position for cervical flexion may be reached, then the FTP may be determined as equal to the maximum CSF pump device position for cervical flexion. The STP of the one or more CSF pumps most adjacent to the cervical spine may be configured to be automatically determined by when force may be sensed by the force transducer coupled to the CSF pump 100 most adjacent to the cervical spine to be at or below some arbitrary force. For example, the head 402 of the user 12 resting on the headrest applies force to the headrest that may be sensed by the force transducer coupled to the CSF pump 100 adjacent to the cervical spine when the cervical spine may be in a neutral anatomic position. The CSF pump Z. Grajcar DKT. NO.408439-X 100 moves the cervical spine into extension, and the force transducer may be eventually experience decreased force when the cervical spine stops easily moving into extension. This increased force may be at or below some arbitrary force that may be used to define the STP of the one or more CSF pumps most adjacent to the cervical spine. If the force at or below some arbitrary force might not be reached but the maximum CSF pump device position for cervical extension may be reached, then the STP may be determined as equal to the maximum CSF pump device position for cervical extension. At FIFTH STEP 310, determine the treatment cycle configured for use during the treatment session. Values may be needed for 4 parameters in a treatment cycle: 1) inhalation phase, 2) hold after inhalation phase, 3) exhalation phase, and 4) hold after exhalation phase. The treatment cycle repeats itself during the treatment session. The values of the parameters of the CSF pump device 10 in the treatment session for the user 12 may be stored in the default CSF pump device prescription database 526. The values of the parameters of the CSF pump device 10 in the treatment session may be used during a later treatment session. During the inhalation phase, each of the one or more CSF pumps moves from the FTP to the STP. Each of the one or more pumps moves synchronously with each of the other one or more pumps from the FTP to the STP. To move synchronously means that each of the one or more CSF pumps may be synchronously at the FTP and the STP during the treatment cycle. Each of the one or more CSF pumps moves in substantially equal linear or rotational distance for a given unit of time from the FTP to the STP. Each of the one or more CSF pumps moves in an acceleration then deceleration pattern in linear or rotational distance for a given unit of time from the FTP to the STP, which may be more comfortable to the user 12 by avoiding an abrupt transition in movement or mimicking the inhalation phase of the user 12 not even using the CSF pump device 10. On the other hand, the substantially equal linear or rotational distance for a given unit of time may cause some discomfort in the user 12 with the abrupt transition from movement in one direction to abruptly stopping for hold after inhalation phase or abruptly reversing direction back to the FTP. However, the substantially equal linear or rotational distance for a given unit of time may be a valid treatment option for some subjects. The inhalation phase may be 1 to 10, 3 to 8, 5 to 10, 2, 4, 6, 7, 8, 9, 10, 11, 12, 13, 14 or more seconds. The inhalation phase may be about 35% to about 45% of the treatment cycle. The inhalation phase may be shorter than the exhalation phase. During the inhalation phase, each of the one or more CSF pumps moves from the STP to the FTP. Each of the one or more pumps moves synchronously with each of the other one or more pumps from the STP to the FTP. To move synchronously means that each of the one or more CSF pumps may be synchronously at the STP and the FTP during the treatment session. Each of Z. Grajcar DKT. NO.408439-X the one or more CSF pumps moves in substantially equal linear or rotational distance for a given unit of time from the STP to the FTP. Each of the one or more CSF pumps moves in an acceleration then deceleration pattern in linear or rotational distance for a given unit of time from the STP to the FTP, which may be more comfortable to the user 12 by avoiding an abrupt transition in movement or mimicking the exhalation phase of the user 12 not even using the CSF pump device 10. On the other hand, the substantially equal linear or rotational distance for a given unit of time may cause some discomfort in the user 12 with the abrupt transition from movement in one direction to abruptly stopping for hold after exhalation phase or abruptly reversing direction back to the STP. However, the substantially equal linear or rotational distance for a given unit of time may be a valid treatment option for some subjects. The exhalation phase may be 1 to 10, 3 to 8, 5 to 10, 2, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14 or more seconds. The exhalation phase may be about 55% to about 65% of the treatment cycle. The exhalation phase may be longer than the inhalation phase. The hold after inhalation phase and the hold after exhalation phase might not be a pattern of breathing used by the user 12 in daily life. However, this pattern of breathing may be used by the user 12 practicing yoga. This pattern of breathing may be known as the box breathing technique. The length of the inhalation phase, the length of the hold after inhalation phase, the length of the exhalation phase, and the length of the hold after exhalation phase may be equal, such as about 4 seconds each. The “box” may be other than a square and may be any quadrilateral shape. The hold after inhalation phase may be optional. The hold after exhalation phase may be optional. The hold after inhalation phase may be present, while the hold after exhalation phase may be absent, as show in FIG.?. The hold after inhalation phase may be absent, while the hold after exhalation phase may be present, as shown in FIG.?. The hold after inhalation phase may be 1 to 10, 3 to 8, 5 to 10, 2, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14 or more seconds. The hold after exhalation phase 1 to 10, 3 to 8, 5 to 10, 2, 4, 5, 6, 7, 8, 9, 10, 11, 12, 13, 14 or more seconds. For simplicity, entered your values have been used for exhalation phase time, inhalation phase time, but one skilled in the art will understand that rather than 7 seconds the phase might last 7.1 seconds, by way of example and not limitation. After all, the percentage of inhalation to exhalation necessitates that fractions of seconds may be involved in the timing of inhalation and exhalation. Furthermore, for simplicity one may describe treatment cycle with 5 second inhalation and 7 second inhalation for a nice neat 5 breaths per minute breath rate. However, one skilled in the art would understand that with the monitoring devices disclosed breath rates may be other than the routinely measured clinical entered your values which are typically recorded as breaths per minute. So, rather than 5 breaths per minute, the user may experience 5.1 breaths per minute, by way of example and not limitation. This information is consistent with the optional 35 Z. Grajcar DKT. NO.408439-X to 45% inhalation phase and 55% to 65% exhalation phase for a breathing cycle. I think that I should have some pizza that you agree At SIXTH STEP 312, determine any other stimulation devices configured to stimulate the user 12 through visual stimulation, auditory stimulation, tactile stimulation, etc. to be applied during the treatment cycle and in what phases of the treatment cycle, and therefore the treatment session. STORE in DATABASE 526 ? At SEVENTH STEP 314, determine any monitoring of the MORE STUFF - questions At EIGHTH STEP 316, activate the control system to operate the CSF pump device 10 and the other stimulation devices during the treatment session made up of the plurality of the treatment cycles. The treatment receives 1 treatment per week, 2 treatments per week, 3 treatments per week, for treatments per week, 5 treatments per week, 6 treat2ments per week, or 7 treatments per week. Each of the treatment sessions may be between about 30 minutes and about 45 minutes. Each of the treatment sessions will be about 15 minutes, about 20 minutes, about 25 minutes, about 30 minutes, about 35 minutes, about 40 minutes, about 45 minutes, or more than about 45 minutes. MONITOR and Record device and store in database 526 STORE RESPONSE TO TREATMENT in DATABASE 526 At STOP 318, stop the method of using CSF pump device. The CSF pump 100 activation may be configured to change a volume of the CSF in the CSF system. The CSF pump 100 may be positioned adjacent to CSF of a user 12. The CSF pump 100 activation may be configured to change curvature of a spinal column of the user 12 to pump the CSF of the user 12. The CSF pump 100 activation may be configured to bend the spinal column of the user 12. The CSF pump 100 activation may be configured to change dynamics of CSF system of the user 12 to improve performance of glymphatic system of the user 12. The CSF pump 100 activation may be configured to change pressure in CSF system of the user 12 to improve performance of glymphatic system of the user 12. The pressure may be configured to cause a peristaltic pumping action of the CSF in a CSF system of the user 12 surrounded by the spinal column. The CSF pump 100 activation may be configured to increase CSF flux of CSF system of the user 12 to improve performance of glymphatic system of the user 12. The CSF pump 100 activation may be configured to increase CSF flow of CSF system of the user 12 to improve performance of glymphatic system of the user 12. The CSF pump 100 activation may be configured to increase level of waste and biological byproducts removed by glymphatic system after the CSF pump 100 may be activated. Z. Grajcar DKT. NO.408439-X The CSF pump 100 activation may be configured to reprogram muscles of the user 12 to increase range of motion about a joint spanned by the muscles. The control system that controls raises the CSF pump 100 adjacent to lumbar region of the spinal column just until a force pad of the CSF pump 100 touches the clothes and / or skin on a posterior portion of a body of the user 12, which may be called the FTP. The operator adjusts the CSF pump 100 to the body of the user 12. The CSF pump 100 may be configured to just touch the clothes and / or skin on posterior surface of body of the user 12, which may be called the FTP. The operator adjusts the CSF pump 100 from the FTP to apply force to the posterior surface to extend the spinal column until extension of the spinal column just exceeds comfortable but not so far as to cause pain in the user 12. The operator adjusts the CSF pump 100 from the FTP to apply force to the posterior surface to extend the spinal column until extension of the spinal column may be configured to produce pain intensity of 1 or 2 out 10 in the user 12 on a medical standard 0 to 10 numerical rating scale for measuring pain intensity. See Neurology 2013;80(Suppl3):S49–S53. The CSF device may be configured to automatically adjust the CSF pump 100 to the body of the user 12. The CSF pump 100 may be configured to just touch the clothes and / or skin on posterior surface of body of the user 12, which may be called the FTP. The operator adjusts the CSF pump 100 from the FTP to apply force to the posterior surface to extend the spinal column until extension of the spinal column just exceeds comfortable but not so far as to cause pain in the user 12. The operator adjusts the CSF pump 100 from the FTP to apply force to the posterior surface to extend the spinal column until extension of the spinal column may be configured to produce pain intensity of 1 or 2 out 10 in the user 12 on a medical standard 0 to 10 numerical rating scale for measuring pain intensity. See Neurology 2013;80(Suppl3):S49–S53, which may be incorporated herein by reference. The operator will raise the CSF pump device 10 adjacent to the spinal column until the force on the spinal column just exceeds comfortable but not so far as to cause pain for the user 12. This distance may be the span that the lumbar flexure device will travel during treatment. The operator of the control system will set the span distance between 20 and 30 mm or between 20 and 25 mm. The CSF pump 100 has a base connected to a force pad, and the force pad may be configured to apply force on the spinal column. The force pad may be moved away from the base and back toward the base to change the curvature of the spinal column. The force pad may be positioned under a lumbar region of the spinal column. The force pad may be positioned under L2 and / or L3 vertebra. The pressure may be applied to thecal sac surrounding a spinal cord of the user 12 and Z. Grajcar DKT. NO.408439-X a cauda equina of the user 12. The force pad may be positioned adjacent to a thoracic region of the spinal column. The CSF pump device 10 may be configured for the span from the FTP to the STP that may be between 20 mm and 30 mm or between 20 mm and 25 mm. The CSF pump device 10 may be configured for the span from the FTP to the STP that may be 1 cm to 5 cm, or 2 cm to 4 cm, or about 3 cm. The CSF pump device 10 may be configured for the span from the FTP to the STP that may be 1 to 5 cm, or 2 to 4 cm. The CSF pump device 10 may be configured for the span from the FTP to the STP that may be 1 cm, 2 cm, 3 cm, 4 cm, or 5 cm. The CSF pump device 10 may be configured for the span from the FTP to the STP that may be 5 to 20 mm, 5 to 15 mm, 5 to 10 mm, 10 to 20 mm, 5 mm, 10 mm, 15 mm, 20 mm, 25 mm, 30 mm, 35 mm, 40 mm, 45 mm, 50 mm, 55 mm, 60 mm, 65 mm, 75 mm, or more. The control system may be configured for the CSF pump device 10. The control system may be configured to increase flexing of the spinal column from a low level at the start of the treatment session during the treatment session. The control system may be configured for the CSF pump device 10 to increase the span between the FTP to the STP over the course of the treatment session. The span of the lumber flexure device may be set to 20 mm at the start of the treatment session and will gradually be increased to 30 mm by the end of the treatment session. The CSF pump 100 will move the spinal column in an arc. The CSF pump 100 will move the cervical segment of the spinal column in an arc. The CSF pump 100 will move the spinal column in flexion and extension from the neutral position, and the amount of flexion may be more or less or equal to the amount of extension. The CSF pump device 10 may be configured for flexion and extension of the cervical segment of the spinal column to be about 10 degrees to about 40 degrees, or about 15 degrees to about 35 degrees, or about 20 degrees to about 30 degrees, or about 25 degrees to about 75 degrees from the neutral position of the cervical spine. The control system may be configured for the CSF pump 100 to increase the arc from the FTP to the second treatment over the course of the treatment session. The CSF pump 100 may be configured for the maximum CSF pump position for cervical flexion of about 40 degrees flexion away from the neutral position of the cervical spine and the maximum CSF pump position for cervical extension of about 40 degrees extension away from the neutral position of the cervical spine. The CSF pump device 10 may be configured for the maximum CSF pump position for cervical flexion of about 30 degrees flexion away from the neutral position of the cervical spine and the maximum CSF pump position for cervical extension of about 30 degrees extension away from the neutral position of the cervical spine. Z. Grajcar DKT. NO.408439-X The control system may be configured to be operated by the operator of the CSF pump device 10 or the user 12 receiving the treatment session from the CSF pump device 10. The control system may be configured to activate the CSF pump device 10. The CSF pump device 10 may be configured to put each of the CSF pump 100s to be the CSF pump 100 to move the cervical spine of the user 12 in position of flexion. The control system may be configured to simultaneously, or synchronously, cause the lumbar flexure device to flex the spinal column a distance equal to the span while the cervical flexure device moves from flexion to extension. Then the control system will simultaneously cause the lumber flexure device to return to the FTP while the cervical flexure device moves from extension to flexion. Extension of the spinal column corresponds to inhalation by the user 12 and flexion of the spinal column corresponds to exhalation by the user 12. Extension of some portion less than all of the spinal column corresponds to inhalation by the user 12. Flexion of some portion less than all of the spinal column corresponds to exhalation by the user 12. The respiration monitor may be configured to monitor inhalation and exhalation of the user 12, record inhalation and exhalation of the user 12, or a combination of monitor and record. The respiration monitor may be configured to monitor the respiration pattern of the user 12, and the treatment cycle may be changed responsive to the respiration pattern. The respiration pattern of the user 12 will automatically switch to match the activity of the CSF pump device 10. The user 12 inhales on extension of the spinal column and exhales on flexion of the spinal column, and the respiration pattern of the user 12 gaits with the activity of the CSF pump device 10 even in the absence of the respiration monitor. The control system may be configured to move the CSF pump device 10 between the FTP and the STP. The CSF pump device 10 comprises one or more of the CSF pump 100s. With the movement of the CSF pump device 10 between the FTP and the STP, each of the one or more of the CSF pump 100s moves between the FTP and the STP for the each of the one or more of the CSF pump 100s. The control system may be configured to move the each of the one or more of the CSF pump 100s between the FTP and the STP. The CSF pump device 10 may be configured to move in a rhythmic fashion from the FTP to the STP and the STP to the FTP, which may be defined as the treatment cycle. The CSF pump device 10 may be configured to move each of the one or more of the CSF pump 100s back and forth between the FTP and the STP, which may be defined as the treatment cycle. The CSF pump device 10 may be configured to move each of the one or more of the CSF pump 100s between the FTP and the STP, which may be defined as the treatment cycle. The first of one or more of the treatment cycles for the user 12 begins with each of the one or more CSF pumps in the FTP. The FTP corresponds to beginning inhalation or ending exhalation Z. Grajcar DKT. NO.408439-X by the user 12. The first movement of the CSF pump device 10 may be from the FTP to the STP. The STP corresponds to ending inhalation or beginning inhalation by the user 12. The movement from the FTP to the STP and from the STP to the FTP may be different speeds. Movement from the FTP to the STP may be performed in the first time period and movement from the STP to the FTP may be performed in the second time period, wherein the second time period may be generally greater than the first time period. The treatment cycle may take between 10 and 15 seconds, with the time from the FTP to STP taking about 35% to about 45% of the treatment cycle time and the time from the STP to the FTP taking about 55% to about 65% of the treatment cycle time. The treatment cycle time may take between 8 and 15 seconds. Other values of the treatment cycle are contemplated, such as the treatment cycle taking between 8 and 15 seconds. The CSF pump device 10 may be configured to move from the FTP to the STP in a period of 1 second to 10 seconds, 3 seconds to 8 seconds, 4 seconds to 10 seconds, 5 seconds to 10 seconds, 2 seconds, 3 seconds, 4 seconds, 5 seconds, 6 seconds, 7 seconds, 8 seconds, 9 seconds, 10 seconds, 11 seconds, 12 seconds, 13 seconds, 14 seconds or more. The CSF pump device 10 may be configured to move from the STP to the FTP in a period of 1 second to 10 seconds, 3 seconds to 8 seconds, 4 seconds to 10 seconds, 5 seconds to 10 seconds, 2 seconds, 3 seconds, 4 seconds, 5 seconds, 6 seconds, 7 seconds, 8 seconds, 9 seconds, 10 seconds, 11 seconds, 12 seconds, 13 seconds, 14 seconds or more. The CSF pump device 10 may be configured to provide the user 12 with from 1 to 7 or more treatment sessions in a week. The treatment session comprises a plurality of the treatment cycles. The treatment session has a duration between 30 and 45 minutes, or the treatment session has a duration of 10 minutes, 15 minutes, 20 minutes, 25 minutes, 30 minutes, 35 minutes, 40 minutes, or 45 minutes or more. The environment may be configured to place the user 12 in a low brain activity state. The user 12 may be provided with auditory, visual, or tactile stimulation or a combination thereof to place the user 12 in the low brain wave activity state. The user 12 may be induced to sleep to place the user 12 in the low brain wave activity state. The brain wave activity state of the user 12 may be monitored by electroencephalography (EEG). An apparatus may be positioned on a body of the user 12 and configured to provide oscillating pressure to improve performance of lymphatic system of the user 12. The body may be an upper body of the user 12. The body may be a limb of the user 12. An apparatus may be positioned on a body of the user 12 and configured to provide oscillating pressure to improve performance of glymphatic system of the user 12. The body may be an upper body of the user 12. The body may be a limb of the user 12. An apparatus may be Z. Grajcar DKT. NO.408439-X configured to provide oscillate force on an upper body of the user 12 to cause increased lymphatic system performance. Administering a treatment to predetermined target in central nervous system of the user 12 through increased CSF flow of CSF system of the user 12 through improved performance of glymphatic system of the user 12 after activating the CSF pump 100. The CSF flow of the CSF system of the user 12 may be optimized for administering the treatment to the predetermined target in the central nervous system by the control system being configured to vary rate of CSF flow. For example, the control system may be configured to increased CSF flow to drive the treatment to predetermined target, and then the control system may be configured to decrease CSF flow to increase a dwell time of the treatment to the predetermined target, followed by the control system may be configured to increase CSF flow to increase a rate of clearance of the treatment and any associated products from the treatment from the CSF system through optimization of glymphatic clearance. The CSF pump 100 activation may be configured to increase flow of CSF in periarterial pathways of the user 12. The CSF pump 100 activation may be configured to increase flow of CSF in perivenous pathways of the user 12. The CSF pump 100 activation may be configured to increase periarterial CSF flux in peri-vascular spaces of a brain of the user 12. The CSF pump 100 activation may be configured to increase filtration of CSF of the user 12 to cause increased generation of CSF of the user 12. The CSF pump 100 activation may be configured to increase filtration of CSF and generation of CSF to cause increased CSF flow in periarterial spaces and perivenous spaces of the user 12. The CSF pump 100 activation may be configured to increase filtration of CSF and generation of CSF to cause increased CSF flow in periarterial spaces and perivenous spaces of the user 12. The CSF pump 100 activation may be configured to increase periarterial and perivenous CSF flow to cause an increase of removal of metabolic waste and / or beta-amyloids from a brain of the user 12. The CSF pump 100 activation may be configured to increase filtration and generation of CSF to cause a lowered concentration of metabolic waste products in the CSF in a periarterial space of the user 12. The CSF pump 100 has a force pad that may be movable. The force pad may be positioned adjacent to a spinal column posterior of a body of the user 12. The CSF pump 100 when activated moves the movable pad towards anterior of the body and then back towards the posterior of the body. The force pad may be configured to cause a curvature of the spinal column resulting in a flexing of the spinal column. Changing the curvature of the spinal column causes the CSF flux of the CSF system in a central nervous system of the user 12 to be at an increased level as compared to the CSF flux of the CSF in the central nervous system prior to activating the CSF pump 100. Z. Grajcar DKT. NO.408439-X The CSF pump 100 activation may be configured to apply force to a spinal column of the user 12 to cause a pressure increase in CSF in a thecal sac of the user 12. The CSF pump 100 activation may be configured to increase pressure of CSF in a thecal sac of the user 12 to cause increased filtration of CSF of the user 12. The CSF pump 100 activation may be configured to be surgically connected to a cistern or ventricle of the CSF system, and the CSF pump 100 activation may be configured to create a pressure gradient in the CSF system. The CSF pump 100 may be positioned outside of a CSF system of the user 12. A force pad attached to the CSF pump 100 may be positioned posterior of a spinal column of the user 12, and the force pad may be configured to move in an anterior and a posterior motion in relation to the user 12. A chair may be provided to support the user 12, the chair providing an opening, a force pad may be positioned within the opening; and the CSF pump 100 activation may be configured to cause the force pad to change the dynamics of the CSF system. The user 12 may be administered a stimulation selected from the group consisting of electrical energy, electromechanical energy, electromagnetic energy, sound, visual images, or a combination thereof to help place the user 12 in the low brain activity state. Electrical, audio, electromagnetic, or mechanical stimulation may be provided to the user 12. The CSF pump 100 activation may be configured to not remove or add CSF to a CSF system of the user 12. The CSF pump 100 may be positioned adjacent to a cervical segment of the spinal column. The CSF pump 100 may be activated to change curvature of the cervical region of the spinal column. The CSF pump 100 activation provides flexion or extension of the cervical region. A chair may be provided to support the user 12, a backrest may be provided in the chair configured to support a back of the user 12, the CSF pump 100 may be positioned in the backrest, and a force pad attached to the CSF pump 100, the force pad configured to apply force to the spinal column. A headrest may be provided in the chair configured to support a head 402 of the user 12, and a second pump may be positioned to move the headrest configured to cause flexion and extension of the spinal column. The force pad may be moved between a FTP and STP. The force pad may be cycled between the FTP and the STP. The force pad may be moved for a first time period from the FTP to the STP, and the force pad may be moved for a second time period from the STP to the FTP, wherein the second time period may be greater than the first time period when cycling the force pad. The chair position may be configured to put the user 12 a zero-gravity position. Z. Grajcar DKT. NO.408439-X The method comprises providing electrical, audio, electromagnetic, or mechanical stimulation to the user 12. The CSF pump device 10 may be configured to change the CSF dynamics of the user 12. The stimulation devices may be configured to provide stimu...

Claims

Z. Grajcar DKT. NO.408439-X ABSTRACT Therapeutic support device, systems, and methods are directed towards optimizing cerebrospinal fluid dynamics in patients and otherwise healthy individuals. In some embodiments, a therapeutic support device may comprise a base, a thigh rest frame supported by the base and a back frame supported by the base. A back support may be attached to the back frame. A headrest may be movable with respect to the back frame about a headrest access. The back support may define a reference plain. They headrest access may be oriented to a front side of the reference plane and the back frame oriented to a second side of the reference plane.USPTO Claims Dkt. No.408439-037 a headrest actuation mechanism arranged to move the headrest about the headrest axis.

8. The therapeutic support device of claim 1, wherein the headrest is moveable about the headrest axis between a first treatment position and a second position, the second position rotated at least 90 degrees with respect to the first treatment position.

6. The therapeutic support device of any of claims 3, wherein the cerebrospinal fluid pump is configured to move the distance from the first treatment position to the second treatment position in a profile characterized as a sinusoidal curve.

7. The therapeutic support device of any of claims 3, wherein the acceleration occurs in approximately an initial one third of the second prescribed time.

8. The therapeutic support device of any of claims 3, wherein the deceleration occurs in approximately a last two thirds of the second prescribed time.

9. The therapeutic support device of any of claims 1 to 8, further comprising: an adjustment mechanism configured to position a cerebrospinal fluid pump in a treatment position that fits a subject for treatment cycles of a treatment session; and an actuation mechanism configured for cyclic movement of the cerebrospinal fluid pump between a first treatment position and a second treatment position during the treatment cycles of the treatment session to change cerebrospinal fluid dynamics of the subject.

10. The therapeutic device of claim 9, further comprising: a control system configured to control the adjustment mechanism to position the cerebrospinal fluid pump in the treatment position.

11. The therapeutic support device of claims 9-10, further comprising: a control system configured to control the actuation mechanism responsive to a heart rate variability of the subject. 2USPTO Claims Dkt. No.408439-037 12. A method for making a therapeutic support device for improving glymphatic clearance, which comprises: providing a pump whose activation is configured to flex a cerebrospinal fluid system of a subject; and providing a control system configured to control a volume of the cerebrospinal fluid in the cerebrospinal fluid system or a part thereof.

13. The method of claim 12, further comprising: providing the control system configured to decrease the volume of the cerebrospinal fluid in the cerebrospinal fluid system of the subject with a condition of increase in the volume of the cerebrospinal fluid in the cerebrospinal fluid system in relation to a normal state.

14. The method of claim 12, further comprising: providing the control system configured to decrease a volume of an interstitial fluid from a central nervous system of the subject with a condition of increase in the volume of the interstitial fluid in the central nervous system in relation to a normal state.

15. The method of claim 12, further comprising: providing the control system configured to remove toxins from central nervous system of the subject.

16. A neurofluid coherence device comprising: a first physiologic sensor configured to measure a first physiologic parameter in a subject; a second physiologic sensor configured to measure a second physiologic parameter in the subject; a physiologic stimulator configured to stimulate the subject; and a processor configured to modulate the physiologic stimulator responsive to a temporal coherence of a first physiologic parameter wave of the first physiologic parameter and a second physiologic parameter wave of the second physiologic parameter, wherein the temporal coherence expresses a probability of waves to interfere at different points in 3USPTO Claims Dkt. No.408439-037 time, wherein the first physiologic sensor is configured to measure vasomotion in a brain of the subject.

17. The neurofluid coherence device of claim 16, wherein the second physiologic sensor is configured to measure heartrate in a heart of the subject.

18. The neurofluid coherence device of claims 16, wherein the second physiologic sensor is configured to measure breath rate in a lung of the subject.

19. The neurofluid coherence device of claim 18, further comprising: a third physiologic sensor configured to measure heartrate in a heart of the subject, and the processor is configured to modulate the physiologic stimulator responsive to the temporal coherence of the first physiologic parameter wave of the first physiologic parameter, the second physiologic parameter wave of the second physiologic parameter, and a third physiologic parameter wave of the third physiologic parameter.

20. The neurofluid coherence device of claims 16 to 19, wherein the physiologic stimulator is configured to move cerebrospinal fluid of the subject. 4

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