Research ArticleNEUROSCIENCE

An ultrafast system for signaling mechanical pain in human skin

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Science Advances  03 Jul 2019:
Vol. 5, no. 7, eaaw1297
DOI: 10.1126/sciadv.aaw1297


The canonical view is that touch is signaled by fast-conducting, thickly myelinated afferents, whereas pain is signaled by slow-conducting, thinly myelinated (“fast” pain) or unmyelinated (“slow” pain) afferents. While other mammals have thickly myelinated afferents signaling pain (ultrafast nociceptors), these have not been demonstrated in humans. Here, we performed single-unit axonal recordings (microneurography) from cutaneous mechanoreceptive afferents in healthy participants. We identified A-fiber high-threshold mechanoreceptors (A-HTMRs) that were insensitive to gentle touch, encoded noxious skin indentations, and displayed conduction velocities similar to A-fiber low-threshold mechanoreceptors. Intraneural electrical stimulation of single ultrafast A-HTMRs evoked painful percepts. Testing in patients with selective deafferentation revealed impaired pain judgments to graded mechanical stimuli only when thickly myelinated fibers were absent. This function was preserved in patients with a loss-of-function mutation in mechanotransduction channel PIEZO2. These findings demonstrate that human mechanical pain does not require PIEZO2 and can be signaled by fast-conducting, thickly myelinated afferents.


Cutaneous somatosensory nerve fibers are classified on the basis of their conduction velocity and degree of myelin thickness (1). Rapidly conducting, thickly myelinated cutaneous afferents constitute the Aβ group, whereas slowly conducting, thinly myelinated or unmyelinated afferents belong to the Aδ and C groups, respectively (2, 3). In humans, all cutaneous Aβ afferents are considered to exclusively signal the discriminative aspects of touch, whereas Aδ and C afferents signal pain (“fast” and “slow” pain, respectively) in addition to temperature and affective touch sensations (48). Consistently, the consensus protocol for somatosensory testing in neuropathic pain (9) recommends that the assessment of vibration and punctate touch reflects the functions of Aβ afferents, whereas the assessment of mechanical pain and temperature reflects the functions of Aδ and C afferents. By implication, this suggests that patients with large-fiber neuropathies have intact pain and temperature perception, whereas patients with small-fiber neuropathies have disturbances in these sensory functions.

The dichotomy into a fast system for touch and a relatively slower system for pain fails to recognize that most other species are equipped with an ultrafast pain system comprising nociceptors in the thickly myelinated Aβ range, the prevalence of which varies from 18 to 65% of the myelinated nociceptor population across different species (1013). In the monkey hairy skin, for instance, 12% of the Aβ population consists of nociceptors, representing 18% of the myelinated nociceptor population (12). Further, in humans, high-frequency electrical stimulation of Aβ afferents can generate a painful percept and a nociceptive flexion reflex (14, 15).

In mouse hairy skin, Aβ afferents of the field type, a class of rapidly conducting, brush-sensitive mechanoreceptors, “exhibit hallmarks of myelinated nociceptors” (16). Mouse Aβ field afferents display a high threshold for monofilament activation and capacity to encode noxious skin indentations. These are characteristics of a nociceptor according to the definition by the International Association for the Study of Pain: “a high-threshold sensory receptor of the peripheral somatosensory nervous system that is capable of transducing and encoding noxious stimuli” (17). Another recent paper demonstrates that the stretch-gated PIEZO2 ion channel, which is an important receptor for discriminative touch and proprioception (1820), contributes to mechanical pain signaling in Aδ and C afferents in mice (21).

Here, we used the in vivo electrophysiological technique of microneurography (22) to test whether humans have ultrafast high-threshold mechanoreceptive afferents with nociceptive properties. Given the finding in mice (16), it was hypothesized that these afferents might be the field afferents. We also examined rare patients with selective large- and small-fiber neuropathies to test the hypothesis that lack of Aβ afferents affects psychophysical pain judgments to graded mechanical stimuli (henceforth referred to as mechanical pain sensitivity). Last, we examined patients with an inherited loss-of-function (LOF) mutation in the PIEZO2 stretch-gated ion channel to test the hypothesis that lack of this channel leads to disturbances in mechanical pain sensitivity.


Using microneurography (22), we performed single-unit axonal recordings from the peroneal and radial nerves in 103 healthy participants (112 experimental sessions). We recorded from a total of 157 afferents (peroneal, 129; radial, 28), including all five types of A-fiber low-threshold mechanoreceptors (A-LTMRs) as previously defined in human hairy skin (23): field LTMR (n = 66), rapidly adapting type 1 (RA1) LTMR (hair unit, n = 18), RA2-LTMR (Pacinian unit, n = 4), slowly adapting type 1 (SA1) LTMR (n = 27), and SA2-LTMR (n = 19). All A-LTMR types responded vigorously to soft brush stroking (8).

High-threshold mechanoreceptors with very fast conduction velocities

Besides A-LTMRs, we recorded from 18 A-fiber high-threshold mechanoreceptors (A-HTMRs; Fig. 1A), representing 12% of the A-fiber sample. The receptive field of A-HTMRs comprised multiple small high-sensitivity spots (Fig. 1A). The average size of an A-HTMR receptive field was significantly smaller than the receptive field of field afferents but was not different from that of SA1 afferents (Fig. 1A).

Fig. 1 Humans are equipped with high-threshold and very fast conducting primary afferents.

(A) Location of myelinated HTMR receptive fields from recordings in the peroneal and radial nerves. Each red dot represents the location of an individual A-HTMR (n = 18). The pattern of receptive field spots, mapped with a Semmes-Weinstein monofilament, is shown for two A-HTMRs (marked by arrows; top, radial; bottom, peroneal). Receptive field spots were redrawn on photographic images so they can easily be seen. The horizontal lines represent the medial-lateral dimension, and the vertical lines represent the proximal-distal dimension. The average size of an A-HTMR receptive field, mapped using a filament force six times higher than that for an A-LTMR, was 26.8 mm2 (±6.9; n = 9). This was significantly smaller than the receptive field of field afferents (100.5 ± 7.2 mm2; n = 51; P < 0.0001, Dunnett’s test) but was not different from that of SA1 afferents (41.6 ± 7.5 mm2; n = 17; P > 0.05, Dunnett’s test). (B) Brush responses of an A-HTMR and a field afferent. Using a soft or a coarse brush, the skin area centered on the receptive field of the recorded afferent was gently stroked at 3 cm/s. The field afferent responded vigorously to soft brush stroking. The A-HTMR did not respond to soft brush stroking, but it did respond to coarse brush stroking. The mechanical threshold of this A-HTMR was 4 mN, and the conduction velocity was 52 m/s. It responded to pinching, and its receptive field moved with skin translocation. Freq, frequency. (C) Mechanical threshold distribution of HTMRs and LTMRs in the recorded sample. For RA1 afferents, the preferred stimulus is hair movement, so monofilament thresholds were not measured. For A-HTMR, the median mechanical threshold was 10.0 mN (Q, 5.5–20.0; n = 18). This was significantly higher than the mechanical thresholds of all tested A-LTMR types (at least P < 0.001 for all individual comparisons, Dunn’s test) but was not different from C-HTMRs (10.0 mN; Q, 10.0–27.0; n = 5). (D) Spike activity of an A-HTMR to electrical and mechanical stimulations of the receptive field. Individual electrically and mechanically evoked spikes were superimposed on an expanded time scale to show that the electrically stimulated spike (used for latency measurement) was from the same unit as the one that was mechanically probed at the receptive field. (E) Conduction velocities of HTMRs and LTMRs to surface electrical stimulation (and monofilament tapping in case of one HTMR, conducting at 30 m/s). The data show individual and average (±SEM) conduction velocities of single afferents from peroneal (circles) and radial (diamonds) nerves. Conduction velocities of peroneal A-HTMRs (33.5 ± 2.1; n = 13) were statistically indistinguishable from peroneal A-LTMRs [SA1: 39.8 ± 2.3, n = 10; SA2: 38.6 ± 4.0, n = 4; RA1: 36.8 ± 2.8, n = 6; field: 34.3 ± 1.3, n = 18; F(4,46) = 1.70; P = 0.17, one-way analysis of variance (ANOVA)]. All three peroneal C-HTMRs were conducting at 0.9 m/s. In comparison to the peroneal nerve, conduction velocities of A-fiber types were faster in the radial nerve as expected (A-HTMR: 54.5 ± 2.4, n = 4; SA1: 56.8 m/s, n = 1; SA2: 53.0 ± 3.3, n = 3; RA1: 48.7 ± 1.6, n = 3; field: 47.3 ± 0.2, n = 2) (46). Both radial C-HTMRs were conducting at 1.1 m/s. Conduction velocity of RA2 afferents was not measured. (F) Slowly adapting properties of an A-HTMR at higher indentation forces. Spike activity of a field afferent and an A-HTMR during monofilament stimulation at three different forces, applied using electronic filaments with force feedback. Compared to the field afferent, the A-HTMR showed a sustained response at a lower indentation force (see also fig. S1).

All A-HTMRs were insensitive to soft brush stroking; some did not respond at all, and others produced a weak response comprising one to two spikes (one unit was an exception; see Discussion). Further, A-HTMRs showed no response to joint movement but were activated by coarse brush stroking (Fig. 1B). We also recorded from five C-fiber HTMRs (C-HTMRs), confirmed by the 2-Hz electrical stimulation protocol (24, 25). These C-HTMRs, akin to A-HTMRs, were insensitive to soft brush stroking. For A-HTMR, the median mechanical threshold was 10.0 mN. This was significantly higher than the mechanical thresholds of all tested A-LTMR types but was not different from that of C-HTMRs (Fig. 1C).

On the basis of conduction velocity measurements from 51 peroneal myelinated afferents (Fig. 1, D and E), A-HTMRs were similar to A-LTMRs. A comparison of peroneal with radial (n = 13) data revealed that the average conduction velocity of myelinated fibers in the radial nerve was 16.1 m/s faster than myelinated fibers in the peroneal nerve. The conduction velocities of the fastest A-HTMR were 43.7 and 59.8 m/s in the peroneal and radial samples, respectively.

The A-HTMRs showed rapidly adapting (RA)–like responses at forces near threshold but exhibited slowly adapting (SA)–like responses at higher forces, starting from four to five times threshold (Fig. 1F; for comparison, see fig. S1A for C-HTMR spike activity). The field afferents showed a low-frequency sustained response but at forces that were several hundred times above their threshold (Fig. 1F).

For nine A-HTMRs (≥30 m/s), we tested force-coding properties. The A-HTMRs encoded force in the perceptibly noxious range of indentation (Fig. 2A), and we found a strong correlation between the A-HTMR peak firing rates and psychophysical pain ratings (Fig. 2, B and C; see Fig. 2, D to F, for spike numbers and mean firing and, for comparison, see fig. S1, B and C, for C-HTMR responses to graded punctate forces).

Fig. 2 Neural discharge of A-HTMRs and perception of mechanical pain in response to punctate forces.

(A) Peak discharge rates of human A-HTMRs for monofilament stimulation. The data show individual and average (±SEM) responses of nine A-HTMRs (≥30 m/s) to 5-s monofilament stimulation at eight different indentation forces. A significant linear fit was displayed (R2 = 0.6981, P = 0.0098), and the response at the highest indentation force (3000 mN) was significantly higher than responses to all weaker indentation forces (at least P < 0.05, Dunnett’s test). Individual units are color-coded. (B) Psychophysical data for pain intensity to graded monofilament stimulation. Psychophysical pain ratings were collected from 16 healthy participants (dorsal foot: 8 participants, 12 trial sets; dorsal toe: 8 participants, 9 trial sets) from the microneurography sample. The monofilament force had a significant effect on psychophysical pain ratings [F(8,171) = 29.96; P < 0.0001, two-way ANOVA], with a significant pain of ~14 of 100 emerging at 260 mN, and higher pain ratings with increasing forces (Tukey’s multiple comparisons test). No difference in pain ratings was found between the foot and toe stimulation sites [F(1,171) = 0.1733; P = 0.6777, two-way ANOVA]; hence, the data were pooled for a subsequent analysis. (C) Psychophysical pain ratings as a function of neural discharge in A-HTMRs. A comparison of the average peak discharge rates of nine A-HTMRs and average psychophysical pain ratings for skin indentations (eight forces, 4 to 3000 mN) revealed a significant positive correlation (Pearson r = 0.8944, R2 = 0.8, P = 0.0027). (D) Number of spikes produced by monofilament stimulation in human A-HTMRs. Individual and average (±SEM) responses of nine A-HTMRs to 5-s monofilament stimulation at eight different indentation forces. A significant linear fit was displayed (R2 = 0.6361, P = 0.0177). Individual units are color-coded. (E) Spike activity of an A-HTMR during the first 0.5 s of monofilament stimulation (with force feedback). Top: Neural discharge rates. Middle: Spike markers and indentation force markers. Bottom: Neural recording. The first 0.5 s was selected as the onset period (dynamic phase) of monofilament stimulation (total duration, 5 s). (F) Mean discharge rates of human A-HTMRs for monofilament onset. Individual and average (±SEM) responses of nine A-HTMRs to the onset period (0.5 s) of monofilament stimulation at eight different indentation forces. A significant linear fit was displayed (R2 = 0.6784, P = 0.0120). Individual units are color-coded.

The responsiveness of human field afferents plateaued as the indentation force increased, and we found no correlation with corresponding psychophysical pain ratings (for details on that and other properties of human field afferents, see fig. S2). Collectively, these observations argue against a nociceptive function for human field afferents.

In two A-HTMRs, thermal sensitivity was tested by applying a computer-controlled thermode to the receptive field (TSA-II, Medoc Ltd.): The temperature changed at 1°C/s from a neutral baseline (32°C) to painful end points (4° and 50°C), but no neural response was evoked. In another A-HTMR, radiant thermal stimulation with no mechanical aspect was tested by holding cold and hot objects just above the receptive field (26): The participant readily perceived them as cold and painfully hot, but no neural response was evoked. We also sought to test responses to hair movement or pulling, but the receptive field was often devoid of any visible hairs; in one case, we shaved the receptive field, but this had no effect on the unit’s mechanical sensitivity. In one A-HTMR, we sought to test vibration sensitivity (PIEZO tactile stimulator, Dancer Design, St. Helens, UK): The receptive field itself was not accessible to the vibration probe, so the vibration (1 to 500 Hz) was applied to an adjacent site, but no response was evoked.

Microstimulation of single A-LTMR and A-HTMR afferents produced different sensations

Using single-unit intraneural microstimulation (27, 28), a technique where the same recording electrode is used to electrically stimulate that same single afferent, a painful percept was reported for A-HTMRs (6.3 ± 2.8 μA; 30 Hz; train durations, 0.5 and 1 s) with a spatial overlap between the physiological receptive field and the perceived area of sensation (projected field) in three microstimulated units from the peroneal nerve, each in separate individuals. For unit 1 (conduction velocity, 43.6 m/s), a “sharp” pain sensation was reported and rated as 80 on a pain scale of 0 to 100. For unit 2 (conduction velocity, 41.7 m/s), the pain sensation was described as “pinprick” and rated as 20 on a pain scale of 0 to 100. For unit 3 (conduction velocity, 30.0 m/s), the pain sensation was described as sharp and pinprick, which intensified as the frequency of stimulation was increased (tested up to 300 Hz) (27) with no change in the size or location of projected field. Pain ratings were not collected for this afferent.

Notably, microstimulation of single A-LTMRs never produced a painful percept. We observed overlapping receptive and projected fields in 15 A-LTMRs (6.3 ± 1.0 μA; 1 and 30 Hz; single pulses to train durations of ≤1 s), producing nonpainful mechanical sensations that were described as “vibrating,” “fluttering,” and/or “buzzing” for field afferents (n = 10); fluttering and vibrating for RA1 (n = 1); vibrating for RA2 (n = 1); and “pressure” (n = 2) or buzzing and vibrating (n = 1) for SA1. In two SA1 and an RA1, stimulation frequencies up to 300 Hz were tested (27), which intensified the pressure or vibratory sensation with no change in the size or location of projected field.

Testing in rare patients revealed a critical role for Aβ afferents, but not PIEZO2 stretch-gated channels, in mechanical pain sensitivity

Psychophysical data for graded monofilament stimulation were collected in three patient groups with well-defined rare neuropathies and channelopathies. The first group suffered from sensory ganglionopathy that they acquired as adults and resulted in a complete and permanent loss of large fibers with sparing of small fibers (2931). These patients lacked proprioception and discriminative touch, but their temperature sense was preserved. The second group was selected from a hereditary sensory and autonomic neuropathy cohort type 5 (HSAN-V). This is a congenital disorder involving a mutation of nerve growth factor β gene and results in a reduction of small fibers with sparing of large fibers (3234). Those selected had no temperature perception, but discriminative touch was preserved (see Materials and Methods for other details). The third group also had a congenital disorder involving a PIEZO2LOF mutation and shared symptoms with the patients with Aβ deafferentation including severe tactile and proprioceptive deficits (20, 35).

A comparison of the pain ratings for graded monofilament stimuli (applied to the dorsal foot) revealed significantly lower pain ratings by the patients with Aβ deafferentation compared to the patients with HSAN-V and healthy control participants. The pain ratings of the patients with HSAN-V and healthy participants were not different from each other (Fig. 3A). Sensory testing on the radial forearm of the patients with PIEZO2LOF showed a preserved mechanical pain sensitivity. When the same test was carried out on the forearm of the patients with Aβ deafferentation, no pain emerged at any of the indentation forces (Fig. 3B).

Fig. 3 Mechanical pain sensitivity is dependent on Aβ afferents but not PIEZO2 stretch-gated ion channels.

(A) Psychophysical pain ratings to graded monofilament stimulation of the peroneal foot for two patients with Aβ deafferentation, two patients with HSAN-V and six healthy participants (pooled means ± SEM and individual data comprising mean of triplicates). A comparison of the pain ratings between patients with HSAN-V and healthy participants revealed no effect of condition—healthy versus HSAN-V [F(1,197) = 1.372; P = 0.2428, two-way ANOVA]. In contrast, a comparison of patients with HSAN-V and healthy participants, on one hand, and patients with Aβ deafferentation, on the other hand, revealed a significant effect of condition—healthy versus Aβ deafferentation [F(1,198) = 15.72, P = 0.0001] and HSAN-V versus Aβ deafferentation [F(1,89) = 13.01, P = 0.0005]. ABD, Aβ deafferentation. (B) Psychophysical pain ratings to graded monofilament stimulation of the radial forearm for two patients with PIEZO2LOF, in addition to average pain ratings from four healthy participants (pooled means ± SEM and individual data comprising mean of triplicates). A comparison of the pain ratings between patients with PIEZO2LOF and four healthy participants revealed slightly higher ratings in the patients with PIEZO2LOF compared to healthy participants [F(1,144) = 4.079; P = 0.0453, two-way ANOVA]. The two patients with Aβ deafferentation reported no pain to graded monofilament stimulation of the forearm.


The conduction velocities of the human A-HTMRs were similar to the A-LTMRs, and the properties of human A-HTMRs were in accord with the characteristics of a nociceptor (13, 36). Intraneural microstimulation of single A-HTMRs produced a painful sensation having a sharp/pinprick quality, whereas microstimulation of A-LTMRs always produced nonpainful percepts. The importance of this high-speed system for human pain perception was further suggested by reduced pain ratings to noxious punctate stimuli in patients with Aβ deafferentation and normal pain ratings in patients with HSAN-V. Last, the findings in patients with PIEZO2LOF demonstrated that the ability to grade mechanical pain sensations did not require PIEZO2 channels, suggesting that the function of human A-HTMRs is not critically dependent on this ion channel. The existence of these rapidly conducting pain afferents in humans questions the validity of the dichotomous fast touch–slow pain systems in classical teaching, calls for a reappraisal of the neurological views that mechanical pain examination specifically assesses small-fiber function and that painful neuropathies imply small-fiber involvement, and opens novel therapeutic targets in pain disorders.

Contrary to LTMRs, all HTMRs, except one, were insensitive to soft brush stroking. The sole exception in the A-HTMR sample had a relatively low mechanical threshold (4 mN), which was nonetheless higher than all LTMRs, and displayed other nociceptive properties including coding of noxious force and pain sensation to intraneural microstimulation. The same differential effect vis-à-vis soft brush stroking is known for unmyelinated afferents where C-tactile fibers respond vigorously and C nociceptors are insensitive (25, 37).

When comparing the properties of mouse and human field afferents, it is evident that human field afferents do not have nociceptive properties. That the human field afferents, contrary to their mouse namesake (16), have similar mechanical thresholds to other LTMRs and fail to encode skin indentations in the perceptibly noxious (force) range is clear from our current observations, which are based on the largest sample of field unit recordings in humans.

According to conventional theories, a patient with a selective Aβ fiber neuropathy should have intact mechanical pain sensibility because this is widely believed to be a function of the Aδ system. For example, the quantitative sensory testing protocol of the German Research Network on Neuropathic Pain recommends cold detection and mechanical pain testing for the assessment of the Aδ system (9). Yet, the patients with Aβ deafferentation had normal cold detection but abnormal mechanical pain perception, suggesting that the mechanical pain deficit was related to the loss of Aβ fibers. However, this need not preclude the role of Aδ mechano-nociceptors, and it is unclear whether normal cold thresholds exclude impairment of Aδ mechano-nociceptors in these patients. In contrast to patients with Aβ deafferentation, a subset of patients with HSAN-V had abnormal thermal detection, but mechanical pain perception was normal. These findings suggest that mechanical pain is not exclusively signaled by the small-fiber system, with the clinically important implication being the decoupling of mechanical pain from the Aδ-mediated cold perception and the possibility of perturbed pain perception in Aβ fiber neuropathies.

A recent mouse study (21) showed that PIEZO2 channels contribute to mechanical nociceptive signaling in Aδ and C fibers. However, in three patients with PIEZO2LOF mutation, mechanical pain thresholds were within normal range (35). Here, we were not able to demonstrate any disturbance in pain judgments to graded mechanical stimuli in two patients with PIEZO2LOF mutation. However, PIEZO2 may contribute to aspects of human pain perception that were not captured by our testing protocol. Together, the emerging picture is that mechanical pain in humans is subserved by A-HTMRs but not critically dependent on PIEZO2.

Perhaps, the reason ultrafast nociceptors have received less attention in the animal literature (and have been almost entirely ignored in human work) is that their proportion relative to the overall myelinated nociceptor population decreases from rodents to primates (1013). Another reason is that the thickly myelinated LTMRs likely dominate, by sheer numbers, the wave of the compound action potential (10, 38).

Thickly myelinated nerve fibers are well suited for execution of withdrawal reflexes, given the short latency of signal transmission, as indeed was postulated almost 40 years ago (14, 15). In comparison to C-HTMRs, the A-HTMRs displayed a higher firing rate, a more finely grained receptive field with multiple small high-sensitivity spots, and less propensity for fatigue during sustained noxious mechanical stimulation (tested up to 1 min). These characteristics likely ensure a large, continuous transfer of nociceptive information to the central nervous system with content rich on stimulus quality, localization, and such—features that need not be limited to the ultrafast nociceptors but may apply to varying extents to other types of myelinated nociceptors (3943).

The classification of primary afferents into Aβ and Aδ groups based on conduction velocity is not clear-cut in humans. Therefore, we did not classify the myelinated afferents as Aβ or Aδ in the current study. It is suggested that the “upper border of the main part of the D hair CV [conduction velocity] range” provides “a good indication of the upper end of the Aδ CV range” (10). The limitation of this, however, is in its extrapolation to humans where no detailed account of D hair units exists (39).

In electrophysiological investigations in the monkey, there are two distinct peaks in the conduction velocity distribution (15 and 43 m/s), and the Aβ/Aδ boundary is set “at the minimum between these two peaks, which is 30 m/s” (12). Applying the same Aβ/Aδ boundary to our sample revealed 15 Aβ HTMRs with conduction velocity of ≥30 m/s, representing 88% of the sample of A-HTMRs where conduction velocities were measured (all except one unit). This proportion is higher than that reported for other species (1013) and likely reflects a sampling bias of our study rather than the true proportion of ultrafast nociceptors in humans. In another microneurography study (39), a preponderance of slowly conducting afferents (conduction velocity, <30 m/s) was reported in the A-HTMR sample from the radial nerve with the fastest A-HTMR signaling at 33 m/s.

Single-afferent conduction velocity measurements tend to be lower than those obtained by electrical stimulation of the nerve trunk. Factors such as axonal tapering, branch points, and mechanical/electrical coupling time are thought to be involved (44, 45). The conduction velocities in our sample, measured using electrical stimulation (or mechanical in one case) at the receptive field, are consistent with the data from other studies [e.g., (45)]. Notably, the A-HTMRs and A-LTMRs in our sample had similar conduction velocities. As expected (46), conduction velocities were slower in the lower limb than in the upper limb.

In the current study, we recorded from the cutaneous afferents of the peroneal and radial nerves, but it may be that a high-speed system for mechanical pain signaling exists in deep somatic tissue as well. For instance, in peroneal nerve recordings from human muscle nociceptors (47), a “Group II” nociceptor produced “sharp pain” to intraneural microstimulation with its receptive field located in a tendon at the base of the big toe. This unit had a conduction velocity of 32 m/s; in comparison, the fastest Group III afferent in the sample had a conduction velocity of 13.5 m/s (mean, 6.7 m/s).

The average Aδ propagation velocities in humans as studied using laser- or “epidermal electrical”–evoked potentials are typically in the range of 10 to 15 m/s (48, 49). The latencies of pinprick-evoked potentials are shorter than laser-evoked potentials, thus suggesting a possible contribution of ultrafast A-HTMRs to pinprick-evoked potentials and augmentation thereof (50) in a sensitized state. Further, in the current study, we have shown that electrical activation of ultrafast A-HTMRs (single-unit microstimulation) can evoke a painful percept having a sharp/pinprick quality. We did not track the temporal profile of pain sensation during single A-HTMR microstimulation, e.g., whether it outlasts the stimulus duration, but we aim to explore the resulting perception in more detail in further studies. However, the efficacy of pain therapies based on the gate control theory (51) such as transcutaneous electrical nerve stimulation—a technique using brief, low-intensity electrical pulses to activate Aβ afferents for pain relief—would suggest that the net effect of stimulation of a population of Aβ afferents is not nociceptive [see also (52)]. At the spinal level, at least in mice, fast-conducting cutaneous A-LTMRs project exclusively to deeper laminae of the dorsal horn, whereas fast-conducting cutaneous A-HTMRs project to deeper and superficial laminae (53). The spinal projections of human A-HTMRs remain to be studied.

Slowly conducting, myelinated nociceptors in the human radial nerve (39) show a greater specificity for mechanical stimulation relative to unmyelinated nociceptors, which are often polymodal, an observation that is consistent with other species (13, 36). In the mouse, for instance, there are myelinated nociceptors that respond specifically to high-threshold mechanical stimulation (41) including hair pulling (40); in our sample, the receptive fields of A-HTMRs lacked visible hairs, and we were thus not able to test whether they responded to hair pulling. By implication, the ultrafast A-HTMRs in humans may be highly specific for mechanical stimulation (pure mechano-nociceptors), and we have no observation to the contrary. However, the human A-HTMR population may consist of subpopulations distinguished not only by differences in conduction velocities but also by their response properties. This needs to be systematically tested in a larger population.


We have identified human nociceptors with conduction velocities similar to touch afferents. The ultrafast pain system exists in other mammals, but its existence in humans had hitherto remained a mystery. Further investigations are warranted into their detailed response properties, ion channel properties, and spinal and cortical projections, given the implications for understanding nociception, nocifensive behavior, and clinical pain states.


Single-unit axonal recordings (microneurography) were performed from the left peroneal nerve or the right radial nerve of 103 healthy participants (71 males and 32 females; 20 to 49 years), with some of them recruited more than once with an interval of at least 3 months (112 experimental sessions in total). In 16 participants from the microneurography sample, psychophysical testing for mechanical pain was performed. In addition, psychophysical testing for mechanical pain and thermal testing were performed in two patients with Aβ deafferentation (IW: male, 64 years; GL: female, 69 years) (2931), two patients with HSAN-V (both males, 74 and 86 years) (3234), and six controls (five females and one male; 55 to 67 years). For HSAN-V, a cohort of 23 patients (12 males and 11 females; 25 to 86 years) with confirmed diagnosis were screened for temperature perception, and those with severely diminished temperature perception were selected. Psychophysical testing for mechanical pain was also performed in two patients with PIEZO2LOF (female, 12 years; male, 16 years) (20) and four controls (three males and one female; 20 to 23 years).

All adult participants, as well as guardians of patients with PIEZO2LOF, provided informed consent in writing before the start of the experiment. The study was approved by the ethics committees of Linköping University (dnr 2015/305-31), Liverpool John Moores University (14/NSP/039), and National Institutes of Health’s Combined Neuroscience Ethics Committee (16-AT-0077) and complied with the revised Declaration of Helsinki.

All participants were seated on a chair with legs or arms stretched out (and hand pronated for the radial nerve) and supported with vacuum pillows. Care was taken to ensure that each participant was comfortably seated and well adjusted to room temperature (22°C) before starting the experiment. If subjectively cold, then the participants were covered in a blanket except for the test region. Two microneurography setups were used, henceforth referred to as setups 1 and 2.


The course of the peroneal nerve at the level of the knee was approximated by surface electrical stimulation (1 to 4 mA, 0.2 ms, 1 Hz) using a 2-mm-diameter probe connected to an optically isolated constant-current stimulator (setup 1: FE180 Stimulus Isolator, ADInstruments, Oxford, UK). For radial nerve experiments, the course of the nerve just above the elbow was visualized using ultrasound (LOGIQ e, GE Healthcare, Chicago, IL, USA). A high-impedance tungsten recording electrode was inserted percutaneously, followed by precise localization of the nerve by delivery of weak electrical pulses (0.02 to 1 mA, 0.2 ms, 1 Hz; FHC Inc., Bowdoin, ME, USA). The electrode was insulated, except for the ~5-μm bare tip, with a typical length of 20 mm for the peroneal nerve and 40 mm for the radial nerve (shaft diameter, 0.2 mm). An uninsulated subdermal electrode in an adjacent area served as the reference. A high-impedance preamplifier was taped to the skin near the recording electrode (setup 1: MLT185 headstage, ADInstruments, Oxford, UK), which was used in conjunction with a low-noise high-gain amplifier (setup 1: FE185 Neuro Amp EX, ADInstruments, Oxford, UK). Once the electrode tip was intrafascicular, indicated by the subject’s reports of cutaneous sensations to weak electrical stimulation (≤0.02 mA), the neural activity was amplified. Single LTMRs were searched for by soft brush stroking (1 to 10 cm/s), and single HTMRs were searched for by coarse brush stroking (1 to 10 cm/s) or pinching in the fascicular innervation zone while making small adjustments to the electrode position (25). A soft goat hair brush and a coarse synthetic brush with a bristle length of 30 mm each were used for soft and coarse brush stroking, respectively. A subset of experiments was performed using setup 2 in which the data were digitally sampled using SC/ZOOM developed by the Physiology Section, Department of Integrative Medical Biology, Umeå University.

Unit identification

Individual A-LTMRs (all soft brush sensitive) were separated into RA and SA types on the basis of their adaptive responses to ramp-and-hold indentation of the skin, as per the criteria used in Vallbo et al. (23). Three groups of RA units were identified as follows: Aβ RA1-LTMR (hair unit), responsive to deflection of individual hairs and light air puffs—air puff responses were abolished after hair removal; Aβ field LTMR, comprising multiple spots of high sensitivity with no response to hair displacement or remote tapping of the skin; and Aβ RA2-LTMR (Pacinian unit), comprising a single spot of maximal sensitivity and robust response to remote tapping/vibration. Two groups of SA-LTMRs (types 1 and 2) were identified where several features were examined including spontaneous firing, stretch sensitivity, and receptive field characteristics. In addition, an interspike interval pattern to sustained indentation (100 mN for 30 to 60 s) was tested, where possible, with a skewed and broad pattern for SA1 and a normal distribution for SA2. Coefficients of variation of interspike intervals (23, 54) were 0.80 for SA1 (median; range, 0.32 to 3.53; n = 18) and 0.29 for SA2 (median; range, 0.15 to 0.60; n = 10).

Mechanical threshold and receptive field size of individual units were determined using Semmes-Weinstein monofilaments (nylon fiber; Aesthesio, Bioseb, Pinellas Park, FL, USA). If a unit responded to the same (weakest) monofilament in at least 50% of trials, then it was taken as the mechanical threshold. Measurement of mechanical threshold was the minimum criterion for inclusion in the sample for all LTMR types, except RA1-LTMRs whose preferred stimulus is hair movement, and thus, responsiveness to light air puffs was determined. For receptive field mapping, predetermined monofilament forces of 100 and 600 mN were used for LTMRs and HTMRs, respectively. The receptive field area was estimated by treating it as an ellipse. Latency responses to surface electrical stimulation of the receptive field were captured, which, together with the distance from the stimulation site to the recording electrode, were used to calculate the conduction velocity (in meters per second). Electrically and mechanically evoked spikes were compared on an expanded time scale to ensure that the electrically stimulated unit was the same as the one that was mechanically probed (Fig. 1D). In one instance, the response latency was estimated by rapid mechanical tapping, using an electronic filament, of a receptive field spot.

Mechanical stimulation

The punctate force–coding function of individual units was tested with a range of forces, applied to high-sensitivity spots in the receptive field, using commercially available monofilaments (as mentioned earlier), in addition to custom-built electronic monofilaments that allowed high-resolution (1 ms) force measurements using capacitive sensors (nylon fiber, Physiology Section, Department of Integrative Medical Biology, Umeå University). Each monofilament trial set comprised eight consecutive applications of different forces, applied for 5 s each: 4, 10, 20, 60, 100, 260, 1000, and 3000 mN (corresponding values in pressure, 16, 24, 27, 53, 68, 106, 193, and 292 g/mm2). The trial commenced when the filament came into contact with the skin and lasted until it was withdrawn. When using the commercial apparatus, the start and end of the filament-skin contact were indicated with a push button by the experimenter. Where the recording was stable, data for replicate trials of each monofilament force were collected.

Single-unit intraneural microstimulation

The same recording electrode was also used to stimulate that same axon using low-current electrical pulses (frequencies, 30 Hz to start off; range, 1 to 300 Hz; pulse width, 0.2 ms; intensity (in a microampere range), starting from zero in small increments until a sensation was reported) (27, 55). Stimuli were delivered as single pulses or as trains lasting 0.25 to 1 s. That the same recorded afferent was electrically stimulated depends on the spatial overlap of the evoked percept, i.e., the projected field, with the physiological receptive field (27, 28). This was determined by questioning the participant about the location of the projected field relative to the location of mechanical touch (56). Where a receptive field–projected field overlap was found, sensory qualities of the electrically evoked sensation were noted by asking the participant to describe what they felt; this was followed by a structured questionnaire (28).


In 16 healthy participants from the microneurography sample, psychophysical pain ratings to graded monofilament stimulation of the dorsal foot were collected (dorsal foot, n = 8; dorsal toe, n = 8). Eight monofilament forces were applied for 5 s each, as used in the neural recordings, in random order (three repeats of each force) guided by a custom-written script in MATLAB (R2014b, The MathWorks Inc., Natick, MA, USA). While performing this task, the participants were prevented from viewing the stimuli. Participants were asked to rate the pain intensity on a computerized visual analog scale, ranging from 0 (no pain) to 100 (most intense pain), using the arrow keys of a computer keyboard.

To test whether human Aβ afferents contribute to pain perception and whether this function is dependent on the stretch-gated ion channel PIEZO2, we collected psychophysical data for graded monofilament stimulation in patients with selective deafferentation and those with PIEZO2LOF mutation. The same monofilament protocol was followed in patients as in healthy participants. The only exception was that the patients with Aβ deafferentation could not operate the keyboard themselves—to rate pain intensity on a computerized visual analog scale—because of a complete loss of proprioception. Therefore, they were asked to point at the screen, and the experimenter pressed the keyboard keys accordingly. Patients with PIEZO2LOF also had proprioceptive deficits (20, 35), but they could operate the keyboard.

Psychophysical testing in patients with Aβ deafferentation. IW and GL are well-characterized patients with Aβ deafferentation who suffer from a rare sensory neuronopathy syndrome—a disorder that selectively affects large primary sensory neurons’ cell bodies in the dorsal root ganglia (57)—resulting in a complete and permanent loss of Aβ afferent fibers below C3. However, the cold sensing Aδ system, which is also thought to be the substrate for mechanical pain (9), is intact, as documented in previous clinical and neurophysiological studies (2931). At the start of the experiment, we measured the cold detection threshold, a function of Aδ system, at the dorsal foot/distal leg in triplicates (TSA-II, Medoc Ltd., Ramat Yishai, Israel) and found it to be normal in patients with Aβ deafferentation [means ± SEM, 26.2° ± 0.6°C; controls, 27.0° ± 0.6°C (n = 6); baseline = 32.0°C]. Cold detection was also tested at the dorsal forearm, and the threshold (27.4° ± 0.5°C) was similar to the foot region. In addition to triplicate trials, a more extensive set of 10 cooling trials (interspersed with warming trials) was tested in GL. The detection threshold for the 10 trials was 27.0° ± 0.5°C.

Psychophysical testing in patients with HSAN-V. A mutation in the nerve growth factor β gene, classified as HSAN-V, results in a reduction of Aδ and C fibers with sparing of Aβ fibers, as documented in previous clinical and neurophysiological tests including nerve biopsies and conduction studies (3234). In this well-characterized cohort (n = 23), who were heterozygous for the mutation, thermal and thermal pain testing (dorsal foot; triplicate trials; test range, 20° to 50°C) revealed two subjects who had no cold (<20°C) or heat pain (>50°C) perception, with warm only reported at noxious temperatures (47.5° ± 0.9°C). The corresponding values for controls (n = 6) were 27.0° ± 0.6°C (cold detection), 39.7° ± 0.7°C (warm detection), and 44.0° ± 0.7°C (heat pain threshold). However, HSAN-V subjects were able to detect vibration or focal touch, tested bilaterally at the great toe using a 128-Hz tuning fork or a 100-mN monofilament, as per the protocol defined in the Michigan Neuropathy Screening Instrument (58). Further, sural nerve conduction test was performed in one of them and was within the normal range.

Psychophysical testing in patients with PIEZO2 LOF. In patients with PIEZO2LOF mutation, who had severe proprioceptive and tactile deficits and normal mechanical pain thresholds (20, 35), graded monofilament stimuli were tested for their ability to grade the intensity of mechanical pain. The patients had a history of foot deformities and surgical corrective procedures; thus, testing was preferred in the upper limb (radial forearm). Mechanical pain sensitivity was initially tested in three patients with PIEZO2LOF, but one of them repeatedly fell asleep during the experiment so data could not be reliably collected on him.

Data collection, processing, and analysis

For microneurography setup 1, the neural activity was sampled at 20 kHz, and all data were recorded and processed using the data acquisition and analysis program (LabChart Pro software v8.1.5 and PowerLab 16/35 hardware PL3516/P, ADInstruments, Oxford, UK). Threshold crossing was used to distinguish action potentials from background noise with a signal-to-noise ratio of at least 2:1, followed by template matching to confirm spike morphology.

For microneurography setup 2, the neural signal and forces recorded from the electronic monofilaments were digitally acquired at 19.2 and 1.2 kHz, respectively, using SC/ZOOM (Physiology Section, Department of Integrative Medical Biology, Umeå University). Single action potentials were identified semiautomatically under visual control (59). Before any further data processing, recordings were discarded if the analyses indicated the presence of multiple units or if the signal-to-noise ratio prevented secure action potential identification.

The instantaneous discharge rates were generated as time series with values corresponding to the inverse of interspike intervals. For setup 2, force signals, timing of individual spikes, and the instantaneous discharge rate were exported at 1 kHz from SC/ZOOM to MATLAB (R2014b, The MathWorks Inc., Natick, MA, USA).

For monofilament stimulation, the 500-ms window following the first spike was defined as the trial onset, and similarly, the offset of a trial was defined as the 500-ms window preceding the last spike. In addition, the total period (onset-hold-offset) from the first to the last spike was also analyzed.

For each trial, the number of spikes was counted. The corresponding mean frequency was defined as the number of interspike intervals divided by the sum of the interspike interval duration, and the peak frequency was defined as the maximum value of the instantaneous frequency during the period.

All data were entered in GraphPad Prism for statistical comparisons (version 6.07, GraphPad Software Inc. La Jolla, CA, USA). The type of statistical test used for each comparison is described alongside all statistical data. Figures were generated using CorelDRAW (X8, version, Corel Corporation, Ottawa, ON, Canada).


Supplementary material for this article is available at

Fig. S1. Response properties of C-HTMRs to graded mechanical stimuli.

Fig. S2. Human field afferents do not display nociceptive properties.

This is an open-access article distributed under the terms of the Creative Commons Attribution-NonCommercial license, which permits use, distribution, and reproduction in any medium, so long as the resultant use is not for commercial advantage and provided the original work is properly cited.


Acknowledgments: We thank L. Koppel, A. Kusztor, and R. Liif for recruitment of participants and patients for their involvement. We thank the NCCIH clinical staff team and A. Necaise for arranging the participation of patients with Aβ deafferentation (GL) and PIEZO2LOF. We thank B. Wang for technical support and W. Jung and R. Liif for assistance in some experiments. We thank G. Westling and A. Bäckström for the development of electronic monofilaments. We are grateful to J. Wessberg, M. Heilig, and D. Mahns for reviewing an earlier version of the manuscript and offering advice. Funding: This work was supported by the Swedish Research Council (H.O.), the ALF Region Östergötland (H.O. and S.S.N.), the Pain Relief Foundation (F.M., A.G.M., and F.O.), the Intramural Research Program of the NIH, specifically the NCCIH (A.T.C. and M.C.B.), the DDIR Innovation Award (A.T.C.), and the NINDS (C.G.B.). The PhD stipend of A.M. was funded by the Pain Relief Foundation. Author contributions: H.O., S.S.N., and A.G.M. developed the experimental protocol with input from F.M. and M.T. S.S.N., A.G.M., E.J., and A.M. performed the microneurography experiments with assistance from S.S. and F.O. S.S.N. performed the psychophysical experiments in healthy participants. J.L. performed the psychophysical testing in patients with Aβ deafferentation (GL) and PIEZO2LOF with input from M.C.B., A.T.C., D.S., S.D., A.R.F., and C.G.B. S.S.N. performed the psychophysical testing in patients with Aβ deafferentation (IW) and HSAN-V with input from J.C., J.M., and M.R. S.S.N., E.J., and A.G.M. analyzed the electrophysiological data. S.S.N and E.J. produced the figures. S.S.N. wrote the paper with input from all other authors. Competing interests: The authors declare that they have no competing interests. Data and materials availability: All data needed to evaluate the conclusions in the paper are present in the paper and/or the Supplementary Materials. Additional data related to this paper may be requested from the authors.

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