METHOD AND DEVICE FOR ENHANCING MEMORY CONSOLIDATION

Abstract

The present invention relates to methods and devices to consolidate memory and/or cognitive functions by monitoring brain rhythms and delivering a stimulus at an appropriate stage of sleep cycle.

Claims

1.-15. (canceled)

16. A non-invasive method for monitoring a subject's brain activity and emitting stimuli according to said subject's brain activity, said method comprising: I. receiving a brain activity signal measured by a monitoring device for measuring said subject's brain activity; II. monitoring said brain activity signal, III. detecting in said brain activity signal an end of a stage I of a non-REM light sleep state, by detection of a negative peak with an amplitude inferior to 75 V, and an onset of a stage II of said non-REM light sleep state, IV. emitting a first stimulus at the detection of the onset of stage II of said non-REM light sleep state, V. emitting a second stimulus, VI. repeating emitting the first stimulus and the second stimulus until an end of a stage IV of said non-REM light sleep state, and VII. restarting steps IV to VII when an onset of a further stage II of said non-REM light sleep state is detected.

17. The non-invasive method according to claim 16, wherein said first or second stimulus is a sensory, electrical and/or magnetic stimulus.

18. The non-invasive method according to claim 16, wherein both stimuli are separated for a time comprised from about 0.5 second to 2.5 seconds.

19. The non-invasive method according to claim 16, wherein the first stimulus is emitted from about 0.1 to about 1 second after the detection of the negative peak in said brain activity signal.

20. The non-invasive method according to claim 16, further comprising emitting same stimuli during a memory training or a learning process while said subject is awake.

21. The non-invasive method according to claim 16, wherein said method is controlled by said subject.

22. The non-invasive method according to claim 16, wherein said method is controlled by a skilled physician.

23. The non-invasive method according to claim 16, wherein said subject is a healthy subject which undergoes normal aging or a training period.

24. The non-invasive method according to claim 16, wherein said subject is affected by a memory-related disorder or a cognitive-related disorder.

25. The non-invasive method according to claim 16, wherein said subject is affected by a neuronal connectivity disorder.

26. A device for implementing a non-invasive method for monitoring a subject's brain activity and emitting stimuli according to said subject's brain activity, comprising: a. a monitoring device for measuring said subject's brain activity; b. a stimulation device providing at least one type of stimulus; and c. a programmable microcontroller board configured to perform the steps of: I. receiving a brain activity signal measured by said monitoring device; II. monitoring said brain activity signal; III. detecting in said brain activity signal the end of a stage I of a non-REM light sleep state by detection of a negative peak with an amplitude inferior to 75 V and an onset of stage II of a non-REM light sleep state; IV. causing the stimulation device to emit a first stimulus at the detection of the onset of stage II of a non-REM light sleep state; V. causing the stimulation device to emit a second stimulus; VI. causing the stimulation device to repeat the emission of the first stimulus and the second stimulus until an end of stage IV of a non-REM light sleep state; and VII. repeating steps IV to VII when the onset of stage II of a non-REM light sleep state is detected.

27. The device according to claim 26, wherein said stimulus is a sensory, electrical and/or magnetic stimulus.

28. The device according to claim 26, wherein both stimuli are separated by a time interval comprised between 0.5 second to 2.5 seconds.

29. The device according to claim 26, wherein the first stimulus is applied from about 0.1 to about 1 second after the detection of a negative peak in said brain activity signal.

30. The device according to claim 26, further comprising the application of same stimuli during a memory training or a learning process while said subject is awake.

31. The device according to claim 26, further comprising a communication module.

32. The device according to claim 26, wherein said device is controlled by the subject.

33. The device according to claim 26, wherein said device is controlled by a skilled physician.

34. The device according to claim 26, wherein the programmable microcontroller board is further configured to perform a step of filtering said brain activity signal.

35. The device according to claim 26, further comprising a computer-readable storage medium.

36. The device according to claim 26, further comprising a user interface.

37. The device according to claim 26, wherein the user interface is configured to visualize physiological parameters of the subject.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0198] FIG. 1 represents diagrams showing stimulation procedures in human brain.

[0199] FIG. 2 is a histogram showing the effect of stimulation on the amplitude of sleep slow oscillations.

[0200] FIG. 3 is a graph showing the effect of stimulation on the number of slow waves sleep.

[0201] FIG. 4 represents recordings of the sleep architecture before and after stimulation of the human subject.

[0202] FIG. 5 represents diagrams showing recordings and stimulation procedures in the animal model.

[0203] FIG. 6 represents diagrams showing sensory stimulations applied during the down state increase the number of up and down states and SO.

[0204] FIG. 7 represents diagrams showing sensory stimulations in phase with the ongoing up and down state oscillations modulate the pattern of action potential discharge in sensory cortical neurons.

[0205] FIG. 8 represents recordings of SO shapes alongside with a stimulation phase histogram of a fixed double stimulation protocol (A) and an adaptative double stimulation protocol (B).

[0206] FIG. 9 represents diagrams showing recordings, SO detection and stimulation procedures in the animal model. (A). Simultaneous electrocorticographic (ECoG) and intracellular (Vm) recordings from somatosensory pyramidal neurons illustrating the probability of evoking an SO as a function of the stimulation phase (B).

EXAMPLES

[0207] The present invention is further illustrated by the following examples.

Example 1

In Vivo Experiments in Human Brain

[0208] In human subjects, brain activity is monitored online from a single channel (international 10-20 system, FPZ or Fp1 o1r Fp2) referenced to the average potential from electrodes attached to the mastoids (M1 and M2) (FIG. 1-A). During sleep, the stimuli are presented for the first time at the onset of stage 2 (associated with sleep spindles at 11 to 15 Hz) (FIG. 1-B). Furthermore, the stimulations are given at a specific phase of ongoing SO. For this purpose, the EEG is recorded and filtered online below 3 Hz using an equiripple Finite Impulse Response (FIR) filters. Each time the filtered EEG signal crossed an adaptive threshold set at large negative values (default 75 V), two auditory stimulations are triggered (FIG. 1-C). A command sends the sensory stimulation 500 ms after the detection. Then, a second stimulation is provided 1.25 sec after first stimuli. For auditory stimulations, the tones are bursts of pink 1/f noise of 50 ms duration. Sound volume was calibrated to 65 dB SPL. Using this closed-loop feedback system, this system is able to enhance and extend trains of SOs during sleep (FIGS. 2-3). In contrast to previous reports (Ngo H V, et al. 2013 Neuron 78, 545-553), the increased occurrence of SO trains after stimulation translates into an overall increased number of identified SO in SWS. Furthermore, the system induces significant differences in sleep architecture during the stimulation period and extends SWS stages (FIG. 4).

Example 2

In Vivo Experiments in Animals

[0209] Acute experiments in animals are conducted in parallel with human studies. These pre-clinical investigations, by allowing multi-scale (from neuronal population to single neurons) electrophysiological records, offer the possibility to determine the cellular and network mechanisms underlying sensory-evoked SO in humans. Simultaneous in vivo electrocorticographic (ECoG) and intracellular recordings of barrel cortex pyramidal neurons are performed in the anaesthetized rat (Mahon S, et al. (2012) J Neurosci. 32:11377-89; FIG. 1A, left). The barrel cortex is a specific region of the primary sensory cortex which receives and integrates sensory information from the whiskers. Rodents use these highly specialized sensory organs on their snout to constantly acquire sensory information from their environment (Petersen C C et al. Neuron. 2007 Oct. 25; 56(2):339-55). Rats are sedated by a systemic injection of a mixture of ketamine and xylazine, a pharmacological procedure generating a brain activity, including ECoG and intracellular patterns, highly similar to that encountered during SWS in humans and rodents (Destexhe A, et al. 2007 Trends Neurosci. 30: 334-42). In this model, ECoG activity is characterized by the recurrence of SO at 1 Hz reflecting the alternance, at single cortical cell level, of prolonged depolarizations associated with action potential firing (up state, US) and periods of neuronal silence (down state, DS) (FIG. 5-A, right). Whisker stimuli (W Stim.) consisted in short puffs of air at low pressure (50 ms, 4-20 psi) delivered to whiskers contralateral to the site of neuronal recordings. Whisker stimuli were given at specific phases of the up and down states cycle using a close-loop feedback stimulation system (FIG. 5-B). Intracellular activity of single sensory cortical neurons is monitored and an adaptive voltage threshold (VTh) is used to detect transitions between up and down states. When the membrane potential (Vm) fell below Vth, an up to down state transition (UtoD) is detected. Conversely, when Vm rose above VTh, a down to up state transition (DtoU) is detected (FIG. 5-B). A transistor-transistor logic (TTL) pulse commands the sensory stimulation system with a given delay (t) after the detection of the transitions. Varying the time delays after transitions detection permits to explore and determine the best stimulation parameters (delay and intensity) for an optimal enhancement of SO. In some experiments, instead of sensory stimuli, we apply negative and positive direct current pulses through the intracellular electrode to test for changes in the excitability (i.e., the ability to fire an action potential) of cortical neurons during the up and down state cycle (FIG. 5-B). This will allow us to correlate possible changes in cortical excitability with the effectiveness of sensory stimuli in triggering SO.

[0210] Sensory stimuli given more than 150 ms after a transition to the down state are effective in inducing and increasing up down states oscillations in barrel cortex neurons. This effect is also visible at the level of the cortical neurons population expressed as sensory-evoked SO in the EcoG (FIG. 6). Sensory stimulation in phase with the spontaneous ongoing up and down state oscillations (i.e, sensory stimuli at 1 ms after the detection of a DtoU transition) are able to modify the pattern of action potential firing in the up state phase (FIG. 7). This change in firing pattern could be essential for the induction of cortical plasticity (Chauvette S et al. J Neurosci. 2011 Oct. 19; 31(42):14998-5008).

[0211] This is a crucial point since long-term synaptic plasticity is considered as a plausible cellular mechanism underlying sleep-dependent memory formation (Chauvette S et al. 2012 Neuron. 75:1105-13). In future experiments, to determine if sensory stimulations can trigger long-term plasticity at cortical synapses, the amplitude of synaptic responses evoked by local electrical stimulation, or by sensory stimuli, will be compared before and after the application of boosting stimuli. We will also search for long-term modifications in the intrinsic excitability of cortical neurons (Mahon S, et al. 2012 J Neurosci. 32:11377-89) that could also participate to memory formation (Daoudal G, et al. 2003 Learn Mem. 10:456-65).

CONCLUSION

[0212] It is thus expected that our new system can work as an artificial enhancer to boost natural sleep brain waves, including SO but also other sleep oscillations like thalamo-cortical spindles and hippocampal ripples. Because all these sleep oscillations are associated with memory processing, it is anticipated that the system can be applied in clinical settings to restore normal memory performance. Indeed, a number of disorders and diseases are accompanied by changes in sleep patterns and dysfunctions of memory, such as depression (Daoudal G, et al. 2003 Learn Mem. 10:456-65), post-traumatic stress disorder (Steiger A et al. 2013 Pharmacopsychiatry 46 (Suppl.1), S30-S35), Alzheimer's disease (Germain A 2013 Am. J. Psychiatry 170, 372-382) and schizophrenia (Wang G et al. 2011 Trends Neurosci. 34, 452-463). Also, SWS gradually reduces as people age, and may even be entirely absent after 65 or 70. The decline of memory is correlated with a reduction of SWS (Lu W and Goder R 2012 Sleep Med. Rev. 16, 389-394). In normal aging, closed loop stimulation for sleep enhancement can help the maintenance of healthy cognitive function and memory consolidation.

Example 3

Optimized Stimulation Protocols for Enhancing SOs

[0213] The time between the minimum SO deflection and its subsequent maximum is highly variable. Therefore, following a fixed double stimulation protocol (FIG. 8A), it can be observed that, while satisfactory results are obtained for the first stimulation (A, right: stimulation phase histogram alongside the corresponding SO shape), the second stimulation is often not at the maximum of the SO. Therefore we developed an adapted double stimulation protocol in which the stimulation timing is fitted to the SO period (K) and subsequent minimum points. The detection steps of the adaptative protocol (FIG. 8B) are: [0214] 1) Detection of the negative pic (lower than the threshold) of the SO; [0215] 2) Estimation of period K of the current wave (by zero crossing) and stimulation at adapted time K/2; [0216] 3) Detection of the second negative pic and stimulation.

[0217] This protocol gives a better precision for the second stimulation mostly triggered during the maximum of the SO (FIG. 8B, right: stimulation phase histogram alongside the corresponding SO shape).

[0218] Simultaneous electrocorticographic (ECoG) and intracellular recordings from somatosensory pyramidal neurons are performed in rats under ketamine-xylazine (FIG. 9A-B). Slow oscillations (SO) in the ECoG are reflected by an alternation of depolarizing up-states (US) and hyperpolarizing down-states (DS) in cortical neurons. An adaptative voltage threshold (VTh) is used to detect transitions between US and DS. A high-voltage pulse commands the sensory stimulation system (W stim.) with a given delay (t) after the detection of the transitions. Varying the time delays after transitions detection permits to explore and determine the best stimulation parameters for an optimal enhancement of SO. Sensory stimuli delivered during the DS (75 or 150 ms after a transition to the DS) are more effective in triggering new oscillations in cortical neurons and networks compared to sensory stimuli delivered during the US.