SPLASHGUARD DEVICE FOR A WHEELED VEHICLE AND ASSEMBLY COMPRISING SUCH A DEVICE

Description

FIELD OF THE INVENTION

The present invention relates to a respiratory stimulation device, i.e. a device for inducing inhalation and exhalation phases. The invention also relates to methods for controlling the device to induce these inhalation and exhalation phases.

The invention is applicable in the medical field to assist a patient's breathing, increase heart rate variability and re-educate abdominal breathing. The invention can also be used to allow users to improve their breathing. Typically, the invention may be used to induce slow and deep abdominal breathing. With such abdominal breathing, the user can thus feel relaxation, stress regulation or even an improvement in cognitive performance.

In the context of the invention, “abdominal breathing” is characterised by the use of the diaphragm to inhale and exhale. Upon inhalation, the diaphragm descends by contracting, which has the effect of opening the lungs to allow air to enter, and inflating the abdomen. Upon exhalation, the diaphragm rises by relaxing, which has the effect of closing the lungs to allow air to escape, and retracting the abdomen.

PRIOR ART

There are a significant number of people who suffer from stress, anxiety, a lack of psycho-emotional balance or a problem related to cognitive performance. These people have significant tension and chronic tightening of the diaphragm preventing effective abdominal breathing.

To help these people, it is often advisable to perform periods of slow and deep abdominal breathing. To this end, there are several solutions to suggest to a user the optimal phases of inhalation and exhalation in order to obtain this specific breathing. For example, the document WO 2010/088895 or the document U.S. Pat. No. 6,561,987 describes a device for warning the user during the optimal moments of inhalation and exhalation.

The signals transmitted to the user to indicate the optimal breathing phases can take the form of an electric current, an acoustic signal, a visual signal, a temperature variation or else of vibrations.

The disadvantage of this solution is that the user must be focused to follow the signals allowing him to adapt his breathing, so that this respiratory state is difficult to access over long periods or when carrying out another activity.

In addition, some people suffer from respiratory insufficiency and there are also devices intended to control breathing. To this end, it is known to excite the body with vibrations in order to trigger the inhalation phase while allowing the body to generate the exhalation phase itself, as described in the document WO 2021/162555 to combat sleep apnea in infants.

The excitation can also directly target the diaphragm by applying localized vibrations to the abdomen. Such vibrations are for example described in the document WO 2017/198283 which proposes using at least two motors mounted on a lap belt to generate these vibrations in order to stimulate the diaphragmatic muscle. Thus, in the document WO 2017/198283, vibrations of constant amplitudes are applied for a predetermined duration to mechanically stimulate the inhalation phases by activating the diaphragm.

Furthermore, the vibrations of constant amplitudes applied to trigger the inhalation phases can stimulate the parasympathetic nerve and decrease the heart rate, so that this periodic excitation can be used to try to induce a state of relaxation.

However, stimulation of the parasympathetic nerve is not always effective in decreasing the heart rate because the user may also experience excitation of the sympathetic nerve which has the effect of increasing this heart rate. Thus, when the user wears the belt during the day and performs various activities, he very rarely performs periods of slow and deep abdominal breathing with the belt of the document WO 2017/198283.

The technical problem of the invention is therefore to obtain a device that induces the inhalation phases but also the exhalation phases, for example to obtain periods of slow and deep abdominal breathing.

DISCLOSURE OF THE INVENTION

In order to solve this technical problem, the invention proposes to use several vibratory motors juxtaposed on a belt opposite the umbilical region and the sides of the abdomen, and to control these motors to generate variable amplitudes in order to obtain a sensation of movement of the location of the vibrations. In doing so, the user feels an apparent double tactile movement on the abdomen that induces the inhalation and exhalation phases.

Indeed, the invention originates from a discovery according to which the application of a sensation of vibration movement from the sides of the abdomen to the umbilical region allows to induce an abdominal inhalation phase, by actively and progressively inflating the abdomen at the rhythm of the movement of vibrations felt.

In addition, the application of a sensation of vibration movement from the umbilical region to the sides of the abdomen allows to induce an abdominal exhalation phase by actively and progressively retracting the abdomen at the rhythm of the movement of vibrations felt.

Thus, the invention allows to induce both the inhalation and exhalation phases by activating the abdomen and it is now possible to vary these phases to lead a user to perform slow and deep abdominal breathing.

In accordance with a first aspect, the invention concerns a respiratory stimulation device comprising:

• • a belt intended to be fitted around the abdomen of a user;
  • at least three motors fixed to the belt, a central motor and two lateral motors, so as to position the central motor opposite the umbilical region and the lateral motors opposite the two sides of the abdomen of the user when wearing the belt; and
  • a control unit connected to the motors and configured to generate vibrations of variable amplitudes on each motor so as to induce two sensations of movement of the location of the vibration:
  • a first sensation of movement of the location of the vibrations from the sides of the abdomen to the umbilical region obtained by progressively decreasing the amplitude of the vibrations applied to the lateral motors while progressively increasing the amplitude of the vibration applied to the central motor so as to induce inhalation; and
  • a second sensation of movement of the location of the vibrations from the umbilical region towards the sides of the abdomen obtained by progressively decreasing the amplitude of the vibration applied to the central motor while progressively increasing the amplitude of the vibrations applied to the lateral motors so as to induce exhalation.

In the context of the invention, the umbilical region is located below the epigastrium, above the hypogastrium and between the two lateral regions. The sides of the abdomen are located either side of this umbilical region, they can extend over the lumbar and inguinal regions, right and left.

Thus, the invention proposes a lap belt integrating motors activated separately to induce inhalation and exhalation phases. These motors are controlled by a control unit configured to generate the control signals of these motors such that the user feels an apparent double tactile movement on the abdomen which induces the inhalation and exhalation phases.

It is possible to use several waveforms or distinct frequencies to differentiate the vibrations applied during the inhalation phase from those applied during the exhalation phase. The waveforms preferably used may be waves called: “Sinusoidal wave” and “Ricker wavelet”. A sinusoidal wave induces continuous movement and sensation, while Ricker wavelets are spaced by delays to generate a tapping sensation.

It is possible to modify the form of these different waves in order to induce a movement corresponding to the user's expectations. Specifically, the frequency of a sinusoidal wave can vary between 30 Hz and 200 Hz. For Ricker wavelets, it is possible to modify the delay between each tapping sensation which can vary between 0 s and 1 s and the duration of the pulses which can vary between 10 ms and 200 ms. All these parameters, related to the waves, can be controlled by the control unit and thus be recorded in advance.

Differentiation in the forms of the signal for the inhalation and exhalation phases allows to generate different tactile sensations on the abdomen. This differentiation allows the user to distinguish between vibrations that induce exhalations and those that induce inhalations.

Preferably, to allow a suitable perception of the location of the vibrations, each motor has a contact area with the user's body of less than 15 cm². The distance between the central motor and the lateral motors is, for example, of between 10 cm and 20 cm. This distance allows to define a suitable stimulation zone.

At least three motors are needed to induce this apparent double tactile movement on the abdomen. Of course, other motors can be used to improve the sensation of movement of the location of the vibrations and promote breathing phases.

For example, the invention may comprise at least two intermediate motors arranged between the central motor and the lateral motors; the control unit being configured to induce:

• • the first sensation of movement of the location of the vibrations from the sides of the abdomen towards the umbilical region by progressively decreasing the amplitude of the vibrations applied to the lateral motors, while progressively increasing and then decreasing the amplitude of the vibrations applied to the intermediate motors, while progressively increasing the amplitude of the vibration applied to the central motor, so as to induce inhalation; and
  • a second sensation of movement of vibrations from the umbilical region towards the sides of the abdomen by progressively decreasing the amplitude of the vibration applied to the central motor, while progressively increasing and then decreasing the amplitude of the vibrations applied to the intermediate motors, while progressively increasing the amplitude of the vibrations applied to the lateral motors, so as to induce exhalation.

Furthermore, the control unit preferably incorporates wired connection means but it can also integrate wireless connection means so that the user can adjust the respiratory rate induced by the control unit with a smartphone.

Concretely, during the inhalation stimulation phase, the central motor located opposite the umbilical region generates in the first moments of the stimulation a minimum vibration amplitude to reach a maximum amplitude at the end of the stimulation.

On the contrary, the lateral motors located opposite the sides of the abdomen behave inversely by starting the stimulation with a maximum vibration amplitude to tend towards a minimum vibration amplitude at the end of the stimulation.

Thus, in accordance with a second aspect, the invention relates to a method for controlling the respiratory stimulation device so as to induce inhalation phase by generating a sensation of movement of the location of the vibrations, the method comprising the following steps:

• • activating the vibration of the central motor to reach a minimum vibration amplitude;
  • activating the vibration of the lateral motors to reach a maximum vibration amplitude;
  • increasing the vibration of the central motor to reach said maximum vibration amplitude while decreasing the vibration of the lateral motors to reach said minimum vibration amplitude;
  • deactivating the vibration of the central motor; and
  • deactivating the vibration of the lateral motors

Preferably, to obtain efficient activation of the lateral motors, the step of activating the vibration of the lateral motors to reach a maximum vibration amplitude is carried out for a predetermined duration, for example for a duration of between 5 and 15% of the duration of the inhalation stimulation phase, during which the vibration amplitude of the lateral motors increases from the minimum vibration amplitude to the maximum vibration amplitude.

This embodiment allows to limit the strains undergone by the lateral motors during activation to increase their lifespan and also to avoid a sensation of clicking when activating the motors.

In addition, the step of decreasing the vibration of the lateral motors is preferably carried out with at least two speeds: a first speed of decrease slower than a second speed of decrease, and the step of increasing the vibration of the central motor is carried out with at least two speeds: a first speed of increase faster than a second speed of increase; the transition between the speeds of decrease and the speeds of increase may occur at distinct moments of the inhalation stimulation phase.

This embodiment allows to create a simple cross-fade between the two signals in order to improve the perception of the continuity of the apparent movement compared to the use of a single speed of decrease and increase of the vibrations.

Preferably, the step of deactivating the vibration of the central motor is carried out for a predetermined duration, for example for a duration of between 5 and 15% of the duration of the inhalation stimulation phase, during which the vibration amplitude of the lateral motors decreases from the maximum vibration amplitude to the minimum vibration amplitude. This embodiment allows to limit the strains undergone by the central motor during the deactivation step in order to increase its lifespan.

During the exhalation stimulation phase, the lateral motors located opposite the sides of the abdomen generate in the first moments of the stimulation a minimum vibration amplitude to reach a maximum amplitude at the end of the stimulation. On the contrary, the central motor located opposite the umbilical region behave inversely by starting the stimulation with a maximum vibration amplitude to tend towards a minimum vibration amplitude at the end of the stimulation.

Thus, according to a third aspect, the invention relates to a method for controlling the respiratory stimulation device so as to induce an exhalation phase by generating a sensation of movement of the location of the vibrations, the method comprising the following steps:

• • activating the vibration of the central motor to reach a maximum vibration amplitude;
  • activating the vibration of the lateral motors to reach a minimum vibration amplitude;
  • increasing the vibration of the lateral motors to reach said maximum vibration amplitude while decreasing the vibration of the central motor to reach said minimum vibration amplitude;
  • deactivating the vibration of the central motor; and
  • deactivating the vibration of the lateral motors.

Preferably, to obtain efficient activation of the central motor, the step of activating the vibration of the central motor to reach a maximum vibration amplitude is carried out for a predetermined duration, for example for a duration of between 5 and 15% of the duration of the exhalation stimulation phase, during which the vibration amplitude of the central motor increases from the minimum vibration amplitude to the maximum vibration amplitude.

This embodiment allows to limit the strains undergone by the central motor during the activation step to increase its lifespan and also to avoid a sensation of clicking when activating the motor.

Preferably, the step of decreasing the vibration of the central motor is carried out with at least two speeds: a first speed of decrease slower than a second speed of decrease, and the step of increasing the vibration of the lateral motors is carried out with at least two speeds: a first speed of increase faster than a second speed of increase; the transition between the speeds of decrease and the speeds of increase may occur at distinct moments of the exhalation stimulation phase.

This embodiment allows to create a simple cross-fade between the two signals in order to improve the perception of the continuity of the apparent movement compared to the use of a single speed of decrease and increase of the vibrations.

Preferably, the step of deactivating the vibration of the lateral motors is carried out for a predetermined duration, for example for a duration of between 5 and 15% of the duration of the exhalation stimulation phase, during which the vibration amplitude of the lateral motors decreases from the maximum vibration amplitude to the minimum vibration amplitude. This embodiment allows to limit the strains undergone by the lateral motors during the deactivation step in order to increase their lifespan.

BRIEF DESCRIPTION OF THE FIGURES

The manner in which the invention may be carried out and the resulting advantages appear more clearly from the following examples of carrying out, which are given by way of non-limited indication and with the support of the accompanying figures, in which:

FIG. 1 is a schematic representation of the respiratory stimulation device according to a first embodiment of the invention during an inhalation stimulation phase;

FIG. 2 is a schematic representation of the device of FIG. 1 during an exhalation stimulation phase;

FIG. 3 is a graphical representation of the amplitude of the central motor and lateral motors of the device in FIG. 1 during the inhalation and exhalation stimulation phases;

FIG. 4 is a schematic representation of the respiratory stimulation device according to a second embodiment of the invention incorporating intermediate motors; and

FIG. 5 is a graphical representation of the amplitude of the central motor, the intermediate motors and the lateral motors of the device of FIG. 4 during the inhalation and exhalation stimulation phases.

DETAILED DESCRIPTION OF THE INVENTION

FIGS. 1, 2 and 4 show a respiratory stimulation device 10 integrated into a belt 11 fitted around the abdomen of a user. This belt 11 is preferably made of non-abrasive lycra for its extensibility, it can comprise several layers of fabric. In addition, the belt 11 may comprise holding means, for example two Velcro portions arranged on both ends, in order to hold the belt 11 around the user's abdomen during use.

In the example of FIGS. 1 and 2, the belt 11 integrates three motors 12-13. Two of these motors 13, called lateral motors, are arranged opposite the sides of the abdomen 15 and the last motor 12, called central motor, is arranged opposite the umbilical region 14. When the belt 11 is intended for an adult of average proportion, the lateral motors 13 are positioned at a distance D1 of between 10 and 20 cm from the central motor 12.

Of course, if the belt 11 is intended for an infant or an overweight person, the size of the belt 11 and the distance D1 between the motors 12-13 varies.

In addition, FIG. 4 illustrates an embodiment in which the respiratory stimulation device 10 comprises two intermediate motors 16 positioned between the lateral motors 13 and the central motor 12. The distance D2 between the intermediate motor 16 and the lateral motors 13 is of between 5 and 10 cm. Similarly, the distance D3 between the intermediate motors 16 and the central motor 12 is also of between 5 and 10 cm. Each motor 12, 13, 16 preferably has a contact area with the user's body of less than 15 cm².

As before, if the belt 11 is intended for an infant or an overweight person, the size of the belt 11 and the distance D2 and D3 between the motors 12, 13, 16 varies.

All motors 12, 13, 16 are connected to a control unit 30 by wired connectors integrated into the belt. This control unit 30 may be removable to facilitate recharging, for example by using magnetized electrical connectors on the control unit 30. The charging can be carried out by induction or by a connector, for example a USB type connector.

In addition, the control unit 30 can integrate wireless connection means such that the user can adjust the respiratory rate induced by the control unit 30 with a smartphone. Thus, it is possible to modify the adjustment parameters of each motor 12, 13, 16 to adapt to the user's needs.

Indeed, to induce the respiratory phases, the invention proposes to control the motors 12, 13, 16 to vary the vibration amplitude and induce a double tactile movement felt by the user. To this end, the lateral motors 13 are controlled differently from the central motor 12, and from any intermediate motors 16. In the remainder of the description, the difference in control of the lateral motors 13 and the central motor 12 is first presented.

More precisely, during the inhalation stimulation phase P1, the amplitude A13 of the vibrations applied to the lateral motors 13 gradually decreases while gradually increasing the amplitude of the vibration A12 applied to the central motor 12.

This difference in control of the motors 12 and 13 in the inhalation stimulation phase P1 allows to induce an apparent double tactile movement on the abdomen which propagates from the sides of the abdomen 15 to the umbilical region 14, as illustrated in FIG. 1.

On the contrary, during the exhalation stimulation phase P2, the amplitude A13 of the vibrations applied to the lateral motors 13 gradually increases while gradually decreasing the amplitude of the vibration A12 applied to the central motor 12. This difference in control of the motors 12 and 13 in the exhalation stimulation phase P2 allows to induce another apparent double tactile movement on the abdomen which propagates from the umbilical region 14 to the sides of the abdomen 15, as illustrated in FIG. 2.

FIG. 3 is a graphical representation of the amplitude of the motors 12, 13 according to an implementation mode of the different respiratory phases illustrated in FIGS. 1 and 2. More precisely, at the start of the inhalation stimulation phase P1, the amplitude A13 of the lateral motors 13 has the minimum amplitude value Amin. Then, the amplitude A13 undergoes a rapid increase V1 to reach the maximum value Amax at the time T1. Then, the amplitude A13 undergoes a first speed of decrease V2 and reaches an intermediate amplitude value Aint at the time T2. Finally, the amplitude A13 undergoes a second speed of decrease V3 and reaches the minimum value Amin at the end of the duration Ti of the inhalation stimulation phase P1.

For the amplitude A12 of the central motor 12, it starts at the minimum value Amin and undergoes a first speed of increase V4 to reach the intermediate amplitude value Aint at the time T3. Then, the amplitude A12 undergoes a second speed of increase V5 to reach the maximum value Amax at the time T4. Finally, the amplitude A12 undergoes a rapid decrease V6 to reach the minimum value Amin at the end of the duration Ti of the inhalation stimulation phase P1.

Following this inhalation stimulation phase P1, a delay S without vibration is programmed. This delay S, the times T1 to T4, as well as the amplitude values Amin, Aint and Amax, can be parametrized and possibly modified by the control unit 30.

After this delay S, the exhalation stimulation phase P2 begins. In this phase, the amplitude A13 of the lateral motors 13 begins at the minimum value Amin and undergoes a first speed of increase V7 to reach the intermediate value Aint at the time T3. Then, amplitude A13 undergoes a second speed of increase V8 to reach the maximum value Amax at the time T4. Finally, the amplitude A13 undergoes a rapid decrease V9 to reach the minimum value Amin at the end of the duration Te of the exhalation stimulation phase P2.

For the amplitude A12 of the central motor 12, it starts at the minimum value Amin. Then, the amplitude A12 undergoes a rapid increase V10 to reach the maximum value Amax at the time T1. Then, the amplitude A12 undergoes a first speed of decrease V11 and reaches an intermediate value Aint at the time T2. Finally, the amplitude undergoes a second speed of decrease V12 until it reaches the minimum value Amin at the end of the duration Te of the exhalation stimulation phase P2.

At the end of this exhalation stimulation phase P2, a new delay S is applied before starting again a new inhalation stimulation phase P1. This new delay S between the exhalation stimulation phase P2 and the inhalation stimulation phase P1 may be different from the delay S applied between the inhalation stimulation phase P1 and the exhalation stimulation phase P2.

This difference in vibration amplitude between the motors 12 and 13 aims to provide a dynamic tactile sensation on the abdomen. This apparent tactile effect needs to be felt only on the surface of the abdomen in order to induce a motion of vibration movement from the umbilical zone 14 to the sides of the abdomen 15 and from the sides of the abdomen 15 to the umbilical zone 14 to allow the user to consciously synchronize his inhalations and exhalations.

Preferably, the amplitude value Amin is of between 0% and 5% of the amplitude value Amax and the intermediate amplitude value Aint is of between 70% and 90% of the amplitude value Amax. Similarly, the durations Ti and Te of the inhalation and exhalation stimulation phases P1 and P2 may be similar.

In this embodiment, T1 is preferably of between 5% and 15% of the duration Ti of the inhalation stimulation phase P1. T2 is preferably of between 55% and 65% of the duration Ti, T3 is preferably of between 30% and 50% of the duration Ti and T4 is preferably of between 85% and 95% of the duration Ti.

In a variant, the durations Ti and Te may be distinct as well as the times T1 to T4 for the inhalation and exhalation stimulation phases P1 and P2.

All these parameters can be previously stored in the control unit 30 in order to create several stimulation modes that the user can select, for example to induce different types of breathing.

In the embodiment of FIG. 4, the respiratory stimulation device 10 comprises two intermediate motors 16 positioned between the lateral motors 13 and the central motor 12. In this embodiment, the control unit 30 is programmed to generate vibrations of different amplitudes on each motor 12, 13, 16 in order to induce a sensation of movement and to allow the user to consciously synchronize his breathing.

More precisely, during the inhalation stimulation phase P1, the amplitude A12 of the vibrations applied to the central motor 12 progressively increases, while progressively increasing and then decreasing the amplitude A16 of the vibrations applied to the intermediate motors 16, while progressively decreasing the amplitude A13 of the vibration applied to the lateral motors 13.

During the exhalation stimulation phase P2, the amplitude A13 of the vibration applied to the lateral motors 13 gradually increases, while gradually increasing and then decreasing the amplitude A16 of the vibrations applied to the intermediate motors 16, while gradually decreasing the amplitude A12 of the vibrations applied to the central motor 12.

The use of a large number of motors allows to increase the sensation of movement and, thus, to allow the user to better consciously synchronize his breathing and to provide a dynamic tactile sensation to the abdomen in order to induce motions of movement of the vibrations between the umbilical zone 14 and the sides of the abdomen 15 and vice versa.

FIG. 5 is a graphical representation of the amplitude of motors 12, 13 and 16 according to an implementation mode. During the inhalation stimulation phase P1, the amplitude A13 of the signal from the lateral motors 13 starts at a minimum Amin. Then, the amplitude A13 increases to reach the maximum value Amax at the time T5. Then, the amplitude A13 decreases until it reaches the minimum value Amin at the end of the inhalation stimulation phase P1.

For the amplitude A16 of the intermediate motors 16, it starts at the minimum value Amin. Then, the amplitude A16 increases to reach the maximum value Amax at the time T7. Then, the amplitude A16 decreases until it reaches the minimum value Amin at the end of the inhalation stimulation phase P1.

For the amplitude A12 of the central motor 12, it starts at the minimum value Amin and gradually increases to reach the maximum amplitude value Amax at the time T6. Then, the amplitude A12 decreases to reach the minimum value Amin at the end of the inhalation stimulation phase P1.

Following this inhalation stimulation phase P1, a delay S is applied.

After this delay S, an exhalation stimulation phase P2 begins. In this phase, the amplitude A13 of the lateral motors 13 starts at the minimum value Amin and gradually increases to reach the maximum value Amax at the time T6. Then, the amplitude A13 decreases to reach the minimum value Amin at the end of the exhalation stimulation phase P2.

As in the inhalation stimulation phase P1, in the exhalation stimulation phase P2, the amplitude A16 of the intermediate motors 16 begins at the minimum value Amin.

Then, the amplitude A16 increases to reach the maximum value Amax at the time T7. Then, the amplitude A16 decreases until reaching the minimum value Amin at the end of exhalation stimulation phase P2.

For the amplitude A12 of the central motor 12, it starts at the minimum value Amin and gradually increases to reach the maximum amplitude value Amax at the time T5. Then, the amplitude A12 decreases to reach the minimum value Amin at the end of the inhalation stimulation phase P2.

As described above, these values T5 to T7, Amin, Amax, Ti, Te and S can also be adjusted by the control unit 30.

To conclude, the use of two signals of inverse amplitudes applied to the different motors 12, 13, 16 generates a synchronous apparent double tactile movement propagating back and forth between the sides of the abdomen 15 and the umbilical region 14. This apparent double tactile movement allows to induce slow and deep abdominal inhalation and exhalation stimulation phases that allow:

• • to overactivate the function of the sympathetic nervous system if the programmed inhalation time is greater than the exhalation time;
  • to overactivate the function of the parasympathetic nervous system if the programmed inhalation time is less than the exhalation time; or
  • to balance the functions of the sympathetic and parasympathetic nervous system if the programmed inhalation time is equal to the exhalation time.

Activation of the sympathetic nervous system prepares the body to act in response to stress. For example, activation of the sympathetic nervous system speeds up the heart rate while activation of the parasympathetic nervous system slows down the body's functions to put it in a state of relaxation.

Slow and deep breathing of the “cardiac coherence” type allows to stimulate and activate both the sympathetic nervous system and the parasympathetic nervous system. With this specific breathing, the variability of the user's heart rate is improved. This variability being an indicator of good physiological health.

Thus, the invention proposes a device 10 that induces the inhalation and exhalation phases, for example to obtain periods of slow and deep abdominal breathing or to control the heart rate according to the configuration parameters of the induced breathing. The control of the respiratory rate can even improve the physiological health of the user.